US5423808A - Systems and methods for radiofrequency ablation with phase sensitive power detection - Google Patents

Systems and methods for radiofrequency ablation with phase sensitive power detection Download PDF

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US5423808A
US5423808A US08158809 US15880993A US5423808A US 5423808 A US5423808 A US 5423808A US 08158809 US08158809 US 08158809 US 15880993 A US15880993 A US 15880993A US 5423808 A US5423808 A US 5423808A
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electrode
power
means
signal
ablation
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Stuart D. Edwards
Roger A. Stern
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EP Technologies Inc
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EP Technologies Inc
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206Generators therefor
    • AHUMAN NECESSITIES
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    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • AHUMAN NECESSITIES
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    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • A61B18/1492Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
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    • A61B18/14Probes or electrodes therefor
    • A61B2018/1467Probes or electrodes therefor using more than two electrodes on a single probe

Abstract

Systems for ablating tissue control radiofrequency power to an ablation electrode by relying upon actual phase sensitive power measurements, unaffected by phase shifts between radiofrequency voltage and current. The systems also detect these phase differences, if they develop, and integrate this factor in making their control decisions.

Description

This is a continuation of application Ser. No. 08/022,815, filed on Feb. 14, 1993, now abandoned which is a continuation of application Ser. No. 07/789,300 filed Nov. 8, 1991, now abandoned.

FIELD OF THE INVENTION

The invention generally relates to catheters and associated power sources. In a more specific sense, the invention relates to ablation catheters that, once steered and manipulated within interior regions of the body, transmit energy to form lesions for therapeutic purposes.

BACKGROUND OF THE INVENTION

Physicians make use of catheters today in medical procedures to gain access into interior regions of the body to ablate targeted tissue areas. It is important for the physician to control carefully and precisely the emission of energy within the body used to ablate the tissue.

The need for careful and precise control over the catheter is especially critical during procedures that ablate tissue within the heart. These procedures, called electrophysiological therapy, are becoming more widespread for treating cardiac rhythm disturbances.

During these procedures, a physician steers a catheter through a main vein or artery (which is typically the femoral artery) into the interior region of the heart that is to be treated. The physician then further manipulates a steering mechanism to place the electrode carried on the distal tip of the catheter into direct contact with the tissue that is to be ablated. The physician directs radio frequency energy from the electrode tip through tissue to an indifferent electrode to ablate the tissue and form a lesion.

Cardiac ablation especially requires the ability to precisely monitor and control the emission of energy from the ablation electrode.

Conventional systems control radiofrequency power to the ablation electrode based upon root mean squared derivations of the rapidly fluctuating radiofrequency voltage and current. These root mean squared derivations represent real power (PReal) only if the radiofrequency voltage is in phase with the radiofrequency current. When a phase shift develops, the product of the root mean squared voltage and current (also called the apparent power, or PApparent) differ from the real power (PReal) by a factor of the cosine of the phase angle (φ) between the radiofrequency voltage and radiofrequency current, or PReal =PApparent *cosine φ, or PReal =(VRMS *IRMS)*cos φ. Because, PReal takes in account the phase angle (φ), this Specification refers to PReal as "phase sensitive power." They cease having direct relevance to the control decisions that seek to maintain desired power levels at the ablation electrode. In fact, once large phase shifts develop, root mean squared derivations can lead to erroneous control decisions.

SUMMARY OF THE INVENTION

The invention provides an improved system for ablating tissue using radiofrequency energy. The system controls the delivery of radiofrequency energy to the ablation electrode based upon measurements of the phase sensitive power PReal being delivered. The system also detects when a phase shift occurs between radiofrequency voltage and radiofrequency current and takes appropriate action.

In one embodiment, the system includes a source of radiofrequency energy. An electrode assembly emits radiofrequency energy delivered by the source at the ablation site. The system measures radiofrequency current delivered to the electrode assembly and generates a measured radiofrequency current signal. The system also measures radiofrequency voltage at the electrode assembly and generates a measured radiofrequency voltage signal.

According to one aspect of the invention, the system includes a power monitor that multiplies the measured current signal by the measured voltage signal. The monitor thereby derives a phase sensitive power signal that represents the real power (PReal) transmitted to the electrode means. The system includes a controller that performs a function based upon the phase sensitive power signal.

In the preferred embodiment, the controller displays the magnitude of the phase sensitive power signal in a user readable format.

In the preferred embodiment, the controller includes a feedback loop that controls the voltage output of the source based upon the phase sensitive power signal.

According to another aspect of the invention, the system includes a radiofrequency phase shift detector. The detector derives root mean squared current and voltage signal based upon the measured radiofrequency current and voltage signals. The detector multiplies the root mean squared current signal by the root mean squared voltage signal, thereby deriving a root mean squared (PApparent) signal. This signal represents the apparent power transmitted the electrode means.

The detector compares the apparent power (PApparent) signal to the phase sensitive power (PReal) signal generated by the power monitor. The detector generates a deviation signal that indicates the magnitude the phase shift, i.e., phase angle (φ), between the measured radiofrequency voltage signal, where cosine φ equals PReal divided by PApparent and the measured radiofrequency current signal. The detector performs a function based upon the phase shift deviation signal.

In the preferred embodiment, the phase detector interrupts the conduction of radiofrequency energy when the phase shift deviation signal exceeds a predetermined value.

In a preferred arrangement, the source power feedback loop controls the voltage output of the source based upon the phase sensitive power signal when the phase shift deviation signal remains within an prescribed range. If the phase shift deviation signal exceeds this range, the feedback loop reduces the output voltage of the source. If the phase shift deviation signal exceeds a prescribed maximum amount, the feedback loops interrupts power to the electrode assembly.

According to the invention, the system controls radiofrequency power to the ablation electrode by adjusting power output to maintain real power (PReal) at a desired set point. It also detects phase differences between the radiofrequency voltage and current and integrates this factor in making its control decisions.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a system for ablating tissue that embodies the features of the invention;

FIG. 2 is a schematic view of the generator and associated monitor and control circuits for the system;

FIG. 3 is a schematic view of the power monitor and control circuit for the system;

FIG. 4 is a schematic view of the tissue impedance monitor and control circuit for the system;

FIGS. 5A and 5B is a schematic view of the tissue temperature monitor and control circuit for the system;

FIGS. 6A to C are views of an electrode with thermally insulated temperature sensing element that can be used in associated with the system to measure tissue temperature;

FIGS. 7A to C are views of an electrode with multiple thermally insulated temperature sensing elements that can be used in associated with the system to measure tissue temperature; and

FIGS. 8A to C are views of an electrode specially shaped to use in heart valve regions and having multiple thermally insulated temperature sensing elements that can be used in association with the system to measure tissue temperature.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

FIG. 1 shows a system 10 for performing ablation on human tissue that embodies the features of the invention. The system 10 includes a radiofrequency generator 12 that delivers radiofrequency energy. The system 10 also includes a steerable catheter 14 carrying a radiofrequency emitting tip electrode 16.

In the illustrated embodiment, the system 10 operates in a monopolar mode. In this arrangement, the system 10 includes a skin patch electrode that serves as an indifferent second electrode 18. In use, the indifferent electrode 18 attaches to the patient's back or other exterior skin area.

Alternatively, the system 10 can be operated in a bipolar mode. In this mode, the catheter 14 carries both electrodes.

In the illustrated embodiment, the ablation electrode 16 and indifferent electrodes 18 are made of platinum.

The system 10 can be used in many different environments. This specification describes the system 10 when used to provide cardiac ablation therapy.

When used for this purpose, a physician steers the catheter 14 through a main vein or artery (typically the femoral artery) into the interior region of the heart that is to be treated. The physician then further manipulates the catheter 14 to place the tip electrode 16 into contact with the tissue within the heart that is targeted for ablation. The user directs radio frequency energy from the generator 12 into the tip electrode 16 to form a lesion on the contacted tissue.

In the embodiment shown in FIG. 1, the catheter 14 includes a handle 20, a guide tube 22, and a tip 24, which carries the tip electrode 16 (which also will be called the ablation electrode). The handle 20 encloses a steering mechanism 26 for the catheter tip 24. A cable 28 extending from the rear of the handle 20 has plugs (not shown). The plugs connect the catheter 14 to the generator 12 for conveying radiofrequency energy to the ablation electrode 16. The radiofrequency heats the tissue to form the lesion.

Left and right steering wires (not shown) extend through the guide tube 22 to interconnect the steering mechanism 26 to the left and right sides of the tip 24. Rotating the steering mechanism 26 to the left pulls on the left steering wire, causing the tip 24 to bend to the left. Also, rotating the steering mechanism 26 to the right pulls on the right steering wire, causing the tip 24 to bend to the right. In this way, the physician steers the ablation electrode 16 into contact with the tissue to be ablated.

The generator 12 includes a radiofrequency power source 30 connected through a main isolation transformer 32 to first and second conducting lines 34 and 36.

In the illustrated environment, the power source 30 delivers up to 50 watts of power at a frequency of 500 kHz. The first conducting line 34 leads to the ablation electrode 16. The second conducting line 36 leads to the indifferent patch electrode 18.

Monitoring Real and Apparent Radiofrequency Power

As FIGS. 2 and 3 show, the system 10 includes first monitoring means 38 for measuring the radiofrequency current and radiofrequency voltage delivered by the generator 12 to the patient. The first monitoring means 38 also derives control signals indicative of RMS (root mean squared) voltage (in volts), RMS current (in amps), and real power (PReal), also called-phase sensitive power (in watts) to support other control functions of the generator 12.

The first monitoring means 38 may be variously configured and constructed. In the illustrated embodiment, the first monitoring means 38 includes current monitoring means 40 for measuring the radiofrequency current passing from the first line 34 through the tissue to the second line 36 (i.e., from the ablation electrode 16 to the indifferent patch electrode 18).

The first monitoring means 38 also includes voltage monitoring means 42. The voltage monitoring means 42 measures the radiofrequency voltage generated between the first and second conducting lines 34 and 36 (i.e., between the ablation electrode 16 and the indifferent patch electrode 18).

The first monitoring means 38 includes three control outputs 44, 46, and 48.

The first control output 44 carries a signal representative of RMS current conducted by the ablation electrode 16.

The second control output 46 carries a signal representative of the RMS voltage between the ablation electrode 16 and the indifferent patch electrode 18.

The third control output 48 carries a signal representative of the phase sensitive power transmitted by the ablation electrode 16.

In the illustrated embodiment (as FIGS. 2 and 3 show), the current monitoring means 40 includes an isolated current sensing transformer 50 connected in the second conducting line 36. In this arrangement, the current sensing transformer 50 directly measures the radiofrequency current passing through the ablation electrode 16 to the indifferent patch electrode 18.

The measured value is a radiofrequency signal varying at the selected rate, which in the illustrated embodiment is 500 kHz.

The current sensing transformer 50 is connected to the first control output 44, which derives RMS current. The first control output 44 includes an integrated circuit RMS converter 52 to do this function. The RMS current converter first squares the radiofrequency current input signal from the current sensing transformer 50, and then averages the squared signal over a user prescribed period (which in the illustrated embodiment is about once every 0.01 second). The RMS current converter 52 then takes the square root of the average squared value. The resulting output represents RMS current.

The RMS current signal takes the form of a fixed frequency signal whose amplitude varies relatively slowly, when compared with the rapidly varying amplitude of the radiofrequency current input signal.

As FIGS. 2 and 3 show, the voltage monitoring means 42 includes an isolated voltage sensing transformer 54 that is connected between the first and second conducting lines. In this arrangement, the voltage sensing transformer 54 directly measures the radiofrequency voltage across the body tissue between the ablation electrode 16 and the indifferent patch electrode 18.

Like the value measured by the current sensing transformer 50, the measured voltage value is a radiofrequency signal having an amplitude that varies at the selected 500 kHz rate.

The voltage sensing transformer 54 is connected to the second control output 46, which derives RMS voltage. The second control output 46 includes an integrated circuit RMS converter 56 to do this function. The RMS voltage converter 56 squares the radiofrequency voltage input signal and then averages it over the same user prescribed period used by the current converter 52. The RMS voltage converter 56 then takes the square root of the average squared voltage value.

The resulting RMS voltage signal (like the RMS current signal) takes the form of a relatively slowly amplitude signal.

The voltage sensing transformer 54 is also connected to the third control output 48, which derives phase sensitive power. The third control output 48 includes an analog multiplier integrated circuit 58 to do this function. The multiplier circuit 58 receives as one input the radiofrequency input current signal directly from the current sensing transformer 50. The multiplier circuit 58 also receives as a second input the radiofrequency input voltage signal directly from the voltage sensing transformer 54.

The output of the multiplier circuit 58 is the product of these two inputs, which represents the actual radiofrequency power transmitted by the ablation electrode 16.

The power value is (like its component current and voltage inputs) a radiofrequency signal having an amplitude varying at a relatively high radiofrequency rate.

The third control output 48 also includes a low pass filter 60. In the illustrated embodiment, which operates with a radiofrequency rate of 500 kHz, the cut off frequency of the filter 60 selected is about 100 Hz. The rapidly varying measured input power value is low pass filtered by the filter 60 into a relatively slowly amplitude signal.

This signal represents the phase sensitive power signal of the radiofrequency energy that the ablation electrode 16 delivers to the targeted tissue.

The first, second, and third control outputs 44, 46, and 48 each includes appropriate inline scaling circuits 62. The scaling circuits 62 scale the RMS current signal, the RMS voltage signal, and the actual phase sensitive power signal to a specified voltage range that can be usable by the remainder of generator 12 circuitry. In the illustrated embodiment, the scaled range is 0.0 to 5.0 volts.

The first monitoring means 38 also includes an analog to digital converter 64. The converter 64 digitizes a selected one or more of the analog RMS current output signal, RMS voltage output signal, and the phase sensitive power signal.

The digital output(s) of the converter 64 can be used to display measurement results. In the illustrated embodiment, the system 10 includes a first digital display 66 on the generator 12 to show the user the magnitude of the phase sensitive power signal.

The digital output(s) of the converter 64 also can be used to control operation of the generator 12. In the illustrated embodiment, the system 10 uses the digitized outputs in a feedback loop that maintains radiofrequency output voltage within a desired range or at a constant value to control radiofrequency power at the ablation electrode 16. By controlling the power delivered by the generator 12, the physician can reproducibly form lesions of the desired depth during an ablation procedure.

In this arrangement, the system 10 includes an input 68 for the user to enter an operating value desired for the phase sensitive power for the generator 12. The system 10 includes power control means 70 that includes comparator 71 to compare the set point power with phase sensitive power measured by the first monitoring means 38. The output of the comparator varies the output voltage of radiofrequency power source 30 to maintain minimum error between the measured phase sensitive power and the set point power.

In the illustrated embodiment, the power control means 70 also monitors phase differences between radiofrequency voltage and current. The power control means 70 does this function by computing apparent power and by comparing the computed apparent power to the phase sensitive power measured by the first monitoring means 38. If the radiofrequency voltage and current signals are exactly in phase, the apparent power and phase sensitive power will be the same. However, if there is a phase difference, the phase sensitive power will differ from the apparent power by a factor that represents the cosine of the phase angle.

In the illustrated embodiment, the power control means 70 includes a multiplier circuit 72 that obtains the product of the RMS current and RMS voltage. The resulting output of the multiplier circuit 72 forms the apparent (i.e., not phase sensitive) power of the system 10. The power control means 70 includes a comparator 74 to compare the derived apparent power with the phase sensitive power. The magnitude of the output of the comparator 74 quantifies the amount of the phase shift, wherein the cosine of the phase shift φ equals the phase sensitive power (PReal) divided by the apparent power (PApparent), or phase shift φ=cos-1 [PReal /PApparent ].

If the output of the phase shift comparator 74 exceeds a preselected amount, the power control means 70 generates a warning signal to show that a phase shift between the radiofrequency voltage and current has occurred. The system 10 may include a flashing light and audible alarm (not shown) to warn the user.

The power control means 70 operates to maintain a constant set power when the output of the phase shift comparator 74 remains within an allowable range above the threshold amount. The power control means 70 operates to reduce the output voltage of the source 30 when the output of the phase shift comparator 74 increases beyond this range. If the output of the phase shift comparator 74 shows a phase shift beyond a maximum threshold value, the power control means 70 generates a signal to shut off all power to the ablation electrode 16.

Monitoring Tissue Impedance

As FIG. 4 shows, the system 10 further includes second monitoring means 76 for deriving the impedance of the tissue undergoing ablation. The second monitoring means 76 derives tissue impedance not only in absolute terms, but it also serves to record changes in tissue impedance over time.

The second monitoring means 76 generates appropriate control signals based upon observed absolute values of tissue impedance as well as sensed changes according to preprogrammed criteria.

The second monitoring means 76 may be variously configured and constructed. In the illustrated embodiment, the second monitoring means 76 includes a microprocessor 78. The microprocessor 78 samples the digitized outputs of the analog-to-digital converter 64 at prescribed intervals (for example, every 20 milliseconds, which represents a 50 Hz sampling rate).

The microprocessor 78 also divides the sampled digitized RMS voltage signal by the sampled digitized RMS current signal. The digital result is the tissue impedance (in ohms) for the sample. Preferably, the system 10 includes a second display 80 on the generator 12 that shows the user the sampled tissue impedance.

The microprocessor 78 also maintains a record of sampled tissue impedances over time. From this record, the microprocessor 78 calculates the changes in tissue impedance during a selected interval and generates appropriate control signals based upon predetermined criteria.

The predetermined criteria under which the microprocessor 78 generates the control signals based upon tissue impedance can vary. Preferably, the tissue impedance control signals are used to augment the monitoring and control functions of the power control means 70 just described.

In the illustrated embodiment, if measured tissue impedance falls outside a predetermined set range, the microprocessor 78 generates a command signal to shut off power to the ablation electrode 16, whatever the actual phase sensitive power level sensed. The set range for tissue impedance for a cardiac ablation procedure is believed to be about 50 to 300 ohms.

When tissue impedance begins in the set range and, over time, increases beyond it, the most likely cause is the coagulation of blood on the ablation electrode 16. A sudden rise in tissue impedance over the set range suggests the sudden onset of coagulation or a sudden shift in the position of the ablation electrode 16. Rapid fluctuations of the tissue impedance also could suggest poor contact between the ablation electrode 16 and the targeted tissue. All require prompt response; for example, withdrawal and cleaning of the ablation electrode 16, or repositioning of the ablation electrode 16.

The system 10 preferably includes flashing lights and an audible alarm (not shown) to transmit a warning to the user when these conditions occur.

A very high tissue impedance value could suggest poor skin contact with the indifferent electrode 18, or an electrical problem in the system 10. Again, this calls for prompt corrective action.

If tissue impedance remains within the set range, but rises beyond a prescribed amount within the range, the second monitoring means 76 generates a control signal that reduces but does not interrupt, the power output. In this arrangement, a relatively tight range of tissue impedance can be established (for example, 80 to 150 ohms) to maintain relatively constant power within this range.

Monitoring Tissue Temperature

As FIG. 5 shows, the system 10 includes third monitoring means 82 for sensing the temperature of the tissue in contact with the ablation electrode 16. The third monitoring means 82 includes temperature sensing means 84 carried in the ablation electrode 16. The system 10 also includes control means 86 for the generator 12 that is responsive to the sensed tissue temperature for performing generator control functions.

Thermal insulation means 88 thermally isolates the temperature sensing means 84 from the thermal mass of the ablation electrode 16. Thus, the temperature sensing means 84 does not add to or serve as a part of the thermal mass of the ablation electrode 16. It serves to show the true temperature of the tissue with which it is in contact, without adding to the thermal mass of the ablation electrode 16 and without being influenced by the temperature of the surrounding thermal mass of the ablation electrode 16.

In the embodiment illustrated in FIGS. 6A to C, the ablation electrode 16 includes an interior well 90 at its tip end 92. The temperature sensing means 84 occupies this well.

In this arrangement, the thermal insulating means 88 isolates the temperature sensing means 84 from the interior surface of the well 90 and the rest of the thermal mass of the ablation electrode 16.

In FIGS. 6A to C, the temperature sensing means 84 includes a small bead thermistor 94 with two associated lead wires 96 and 98. The temperature sensing tip of the thermistor 94 is exposed at the tip end 92 of the ablation electrode 16 for tissue contact.

In the illustrated embodiment (see FIGS. 6A to C), the third monitoring means 82 includes means 132 for calibrating the thermistor 94 to account for deviations in nominal resistance among different thermistors 94. During manufacture of the catheter 10, the resistance of thermistor 94 is measured at a known temperature; for example, 75 degrees C. A calibration resistor 134 equal to the measured value is incorporated into the catheter handle 20. The leads of the calibration resistor 134 are connected to the third monitoring means 82.

The thermistor 94 of the type shown is commercially available from the Fenwal Co. (Massachusetts) under the trade designation 111-202CAKBD1. The lead wires 96 and 98 comprise #36 AWG signal wire Cu+ clad steel (heavy insulation).

Potting compound 100 encapsulates the thermistor 94 and lead wires 96 and 98 within the electrode well. Insulating sheathes 102 also shields the encapsulated lead wires 96 and 98. Together, the compound 100 and sheathes 102 electrically insulate the thermistor 94 from the surrounding ablation electrode 16.

The potting compound 100 and insulation sheathes 102 can be made with various materials. In the illustrated embodiment, loctite adhesive serves as the potting compound 100, although cyanoacrylate adhesive or RTV adhesive and the like could be used. The sheathes 102 are made from polymide material, although other conventional electrical insulating materials also can be used.

In the illustrated embodiment, the thermal insulating means 88 comprises a tube 104 that envelopes the encapsulated thermistor 94 and lead wires 96 and 98. The thermal insulation tube 104 is itself adhesive bonded to the interior wall of the well 90.

The thermal insulating material of the tube 104 can vary. In the illustrated embodiment, it is a polymide material having a wall thickness of about 0.003 inch. Other thermal insulating materials like mylar or kapton could be used.

The lead wires 96 and 98 for the thermistor 94 extend from the electrode well 90 through the guide tube 22 and into the catheter handle 20. There, the lead wires 96 and 98 electrically couple to the cable 28 extending from the handle 20. A cable plug (not shown) connects to the generator 12 and transmits the temperature signal from the thermistor 94 to the third monitoring means 82.

FIGS. 7A to C show an alternate embodiment of an ablation electrode 16 having an array of temperature sensing means 84. At least one temperature sensing means 84, and preferably all of them, are thermally isolated from the ablation electrode 16 in the manner shown in FIGS. 6A to C.

As FIGS. 7A to C show, the ablation electrode 16 in the multiple array version includes an interior core well 106. Five branch wells 108A to E extend from the core well 106. The branch wells 108A to E open at the surface of the ablation electrode 16. One branch well 108A opens at the tip of the ablation electrode 16, like the single temperature sensing means 84 shown in FIGS. 6A to C. The other four branch wells 100B to E extend at an angle from the core well 106 at arcuate intervals of 45 degrees. The four branch wells 108B to E open at the side of ablation electrode 16 and encircle the tip well branch 100A.

A temperature sensing means 84 occupies each branch well 108A to E. In the illustrated and preferred embodiment, a thermal insulating means 88 isolates each temperature sensing means 84 from the interior surface of the associated branch well 108A to E and the remaining thermal mass of the ablation electrode 16.

As in the embodiment shown in FIGS. 6A to C, each thermal sensing means 84 includes a small bead thermistor 94 with two associated lead wires 96 and 98. The temperature sensing tips of the thermistors 94 are exposed at the tip of the ablation electrode 16 for multiple contact with the tissue. The associated lead wires 96 and 98 are bundled within the center core well 106 and pass through the guide tube 22 to the handle 20.

As in the embodiment shown in FIGS. 6A to C, potting compound 100 encapsulates each thermistor 94 and its lead wires 96 and 98 within the associated branch well. Insulating sheathes 102 also shield the encapsulated lead wires 96 and 98. Together, the compound 100 and sheathes 102 electrically insulate each thermistor 94 from the surrounding ablation electrode 16.

As in the embodiment shown in FIGS. 6A to C, a thermal insulating tube 104 envelopes each electrically encapsulated thermistor 94 and its lead wires 96 and 98. And, as in the FIGS. 6A to C embodiment, adhesive bonds each thermal insulation tube 104 to the interior wall of each branch well 108A to E.

FIGS. 8A to C show another alternate embodiment of an ablation electrode 16 having multiple temperature sensing means 84.

In the arrangement shown in FIGS. 8A to C, the ablation electrode 16 includes a forward electrode region 110 and a rear electrode region 112. The forward electrode region 110 and the rear electrode region 112 are generally spherical in shape.

An electrical and thermal insulating sleeve 114 separates the forward electrode region 110 and the rear electrode region 112. The sleeve 114 is generally cylindrical in shape. The resulting "peanut" shape is well suited for use within the valve regions of the heart.

In the illustrated embodiment, the forward electrode region 110 and the rear electrode region 112 are made of platinum. The sleeve 114 is made of a polysulfone material.

Multiple temperature sensing means 84 occupy the surface of each forward and rear electrode region 110 and 112. At least one, and preferably all, the temperature sensing means 84 are thermally isolated from the remainder of the surrounding body of the associated electrode region 110 and 112.

Each electrode region 110 and 112 includes an interior core well 116 and branch wells 118 that open at the surface of the associated electrode region 110 and 112. A temperature sensing means 84 occupies each well branch. In the illustrated and preferred embodiment, thermal insulating means 88 also isolates each temperature sensing means 84 from the interior surface of the associated branch well 116 and 118 and the rest of the thermal mass of the electrode region 110 and 112.

As in the embodiment shown in FIGS. 6A to C, each thermal sensing means 84 includes a small bead thermistor 94 with two associated lead wires 96 and 98. The temperature sensing tips of the thermistors 94 are exposed at the surface of the associated electrode regions 110 and 112 for multiple contact with the tissue. The associated lead wires 96 and 98 are bundled in the center core well 116, passing through the guide tube 22 to the handle 20.

As in the previous embodiments, potting compound 100 encapsulates each thermistor 94 and its lead wires 96 and 98 within the associated branch well 116 and 118. Insulating sheathes 102 also shield the encapsulated lead wires 96 and 98. Also as in the previous embodiments, a thermal insulating tube 104 envelopes each electrically encapsulated thermistor 94 and its lead wires 96 and 98. Adhesive bonds the thermal insulation tube 104 to the interior wall of each branch well 116 and 118.

The number and arrangement of possible arrays of multiple temperature sensing means 84 can, of course, vary from the specific configurations shown in FIGS. 6, 7, and 8. For example, one or more temperature sensing means 84 can occupy the side region of the ablation electrode 16, below its tip. The branch wells holding the temperature sensing means 84 also can extend from the center well at various angles, acute, obtuse, or perpendicular. Not all the temperature sensing means 84 need be thermally isolated from the electrode 16, but preferable they all are.

As FIG. 5 shows, the third monitoring means 82 can perform different display and control functions in response to sensed temperature conditions according to different prescribed criteria.

Preferably, the third monitoring means 82 responds to sensed tissue temperature not only in absolute terms, but it also serves to record changes in tissue temperature over time and respond to these changes as well.

In the illustrated embodiment, the third monitoring means 82 includes a control output 120 for each temperature sensing means 84 carried by the associated ablation electrode 16.

The lead wires 96 and 98 for each thermistor 94 provide the input for the control outputs 120. Alternatively, when the ablation electrode 16 carries multiple thermistors 94, the number of lead wires 96 and 98 traversing the guide tube 22 can be minimized by providing an integrated circuit 122 within the third monitoring means 82 for multiplexing the input signals of the thermistors 94.

In the illustrated embodiment, the third monitoring means 82 includes a converter 124 to obtain an average temperature for each grouped array of thermistors 94 during a user prescribed period (which in the illustrated embodiment is about once every 0.01 second).

The embodiment shown in FIGS. 6A to C includes one thermistor 94, so the input signal and the average will be the same.

The embodiment shown in FIGS. 7A to C includes a single grouped array of five thermistors 94 clustered at the tip of the ablation electrode 16. For this array, the converter adds the individual input signals and divides by five.

The embodiment shown in FIGS. 8A to C includes two grouped arrays, one having five thermistors 94 on the forward electrode region 110, the other having four thermistors 94 on the rear electrode region 112. The converter 124 adds the input signals for each grouped array and divides by the associated number of thermistors 94 in each grouped array to obtain an average for the forward electrode region 110 and a separate average for the rear electrode region 112.

The third monitoring means 82 includes an analog to digital converter 126. The converter 126 digitizes the sensed temperature average(s) for the system 10.

The converter 126 also digitizes the value of the calibration resistor 134. The thermistor resistance value is divided by the calibration resistor value to get a normalized resistance for the thermistor 94. This value is the input to a read only memory (ROM) 136 (see FIG. 5B) containing stored thermistor temperature data. The ROM 136 output is the actual measured tissue temperature (in degrees C.), taking into account deviations in the nominal resistance of the thermistor 94.

Although not shown in the drawings, the embodiments having multiple thermistors 94 would include an equal number of calibration resistors 134, one for each thermistor 94.

The digital output(s) of the converter can be used to display measurement results. In the illustrated embodiment, the system 10 includes a third digital display 128 on the generator 12 to show the user the average sensed temperature.

If the "peanut" type electrode shown in FIGS. 8A to C is used, the system 10 includes a separate display for the forward and rear electrode region 110 and 112.

The digital output(s) of the converter 126 also can be used to control operation of the generator 12. Preferably, the temperature control signals of the third monitoring means 82 also are used to further augment the function of the first and second monitoring means 38 and 76 previously described.

In the illustrated embodiment, the system 10 uses the digitized temperature outputs in a feedback loop that maintains radiofrequency output voltage within a desired range or at a constant value to control radiofrequency power at the ablation electrode 16. By controlling the power delivered by the generator 12 based upon temperature, the physician is able to control the size of the lesion generated.

For this purpose, the system 10 includes an input 130 for the user to enter an operating value desired for the tissue temperature.

If tissue temperature remains within a preset range, but deviates a prescribed amount within the range, the third monitoring means 82 generates a control signal that either increases or reduces but does not interrupt, the power output. If the tissue temperature rises, the control signal reduces the power output. If the tissue temperature falls, the control signal increases the power output. If measured tissue temperature falls outside the preset range, the third monitoring means 82 generates a command signal to shut off power to the ablation electrode 16. A representative set range for tissue temperature for cardiac ablation is believed to be about 40 degrees to 100 degrees C.

When temperature begins in the set range and, over time, fall outside it, the most likely cause is the coagulation of blood on the ablation electrode 16, requiring withdrawal and cleaning of the ablation electrode 16. A sudden change in tissue temperature outside the set range suggests a shift in the position of the ablation electrode 16, requiring repositioning of the ablation electrode 16.

The system 10 preferably includes flashing lights and an audible alarm (not shown) to transmit a warning to the user when these temperature-based conditions occur.

The system 10 as described can provide precise control over the ablation procedure. The monitoring and control of actual phase sensitive power assure the effective distribution of radiofrequency to the ablation electrode 16. The monitoring and control of tissue impedance and tissue temperature, either separately or in combination, set safe physiological limits in terms of lesion size and detection of coagulation. Monitoring and control of tissue impedance and/or tissue temperature also provide information regarding orientation of the ablation electrode 16.

Claims (8)

We claim:
1. A system for ablating tissue at an ablation site using radiofrequency energy comprising
a source of radiofrequency energy,
an electrode electrically connected to the source for emitting radiofrequency energy at the ablation site,
current monitoring means for measuring radiofrequency current delivered to the electrode and generating a measured radiofrequency current signal,
voltage monitoring means for measuring radiofrequency voltage at the electrode and generating a measured radiofrequency voltage signal,
means for multiplying the measured current signal by the measured voltage signal and deriving a phase sensitive power signal that represents real power (PReal) transmitted to the electrode,
means for deriving a root mean squared current signal based upon the measured radiofrequency current signal,
means for deriving a root mean squared voltage signal based upon the measured radiofrequency voltage signal,
means for multiplying the root mean squared current signal by the root mean squared voltage signal and deriving a root mean squared power signal that represents the apparent power (PApparent) transmitted to the electrode,
means for generating a deviation signal that indicates a phase shift (φ) between PReal and PApparent, where:
φ=cos.sup.-1, and
first control means for performing a function based upon the phase shift deviation signal, and
second control means for performing a function based upon the phase sensitive power signal.
2. A system according to claim 1
wherein the second control means includes display means for showing magnitude of the phase sensitive power signal.
3. A system according to claim 1
wherein the second control means includes
comparator means for comparing the derived phase sensitive power to a desired phase sensitive power and generating a deviation signal, and
command means for varying output voltage of the source in response to the deviation signal.
4. A system according to claim 1
wherein the first control means interrupts conduction of radiofrequency energy when the phase shift (φ) exceeds a predetermined value.
5. A system according to claim 1
wherein the first control means generates a warning signal when the phase shift (φ) exceeds a predetermined value.
6. A system according to claim 1
wherein the second control means controls voltage output of the source based upon the derived phase sensitive power when the phase shift (φ) remains within an prescribed range.
7. A system according to claim 6
wherein the second control means reduces output voltage of the source when the phase shift (φ) increases beyond the prescribed range.
8. A system according to claim 7
wherein the second control means interrupts power to the electrode when the phase shift (φ) exceeds a prescribed maximum value.
US08158809 1991-11-08 1993-11-29 Systems and methods for radiofrequency ablation with phase sensitive power detection Expired - Fee Related US5423808A (en)

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Cited By (251)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5606974A (en) * 1995-05-02 1997-03-04 Heart Rhythm Technologies, Inc. Catheter having ultrasonic device
US5672174A (en) * 1995-08-15 1997-09-30 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5672173A (en) * 1995-08-15 1997-09-30 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5683384A (en) * 1993-11-08 1997-11-04 Zomed Multiple antenna ablation apparatus
US5718702A (en) * 1992-08-12 1998-02-17 Somnus Medical Technologies, Inc. Uvula, tonsil, adenoid and sinus tissue treatment device and method
US5722975A (en) * 1991-11-08 1998-03-03 E.P. Technologies Inc. Systems for radiofrequency ablation with phase sensitive power detection and control
US5728143A (en) * 1995-08-15 1998-03-17 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5728094A (en) * 1996-02-23 1998-03-17 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US5730719A (en) * 1994-05-09 1998-03-24 Somnus Medical Technologies, Inc. Method and apparatus for cosmetically remodeling a body structure
US5735847A (en) * 1995-08-15 1998-04-07 Zomed International, Inc. Multiple antenna ablation apparatus and method with cooling element
US5738114A (en) * 1996-02-23 1998-04-14 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US5743904A (en) * 1996-05-06 1998-04-28 Somnus Medical Technologies, Inc. Precision placement of ablation apparatus
US5743870A (en) * 1994-05-09 1998-04-28 Somnus Medical Technologies, Inc. Ablation apparatus and system for removal of soft palate tissue
US5746224A (en) * 1994-06-24 1998-05-05 Somnus Medical Technologies, Inc. Method for ablating turbinates
US5769847A (en) * 1994-06-27 1998-06-23 Ep Technologies, Inc. Systems and methods for controlling tissue ablation using multiple temperature sensing elements
US5782827A (en) * 1995-08-15 1998-07-21 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method with multiple sensor feedback
US5800379A (en) * 1996-02-23 1998-09-01 Sommus Medical Technologies, Inc. Method for ablating interior sections of the tongue
US5810804A (en) * 1995-08-15 1998-09-22 Rita Medical Systems Multiple antenna ablation apparatus and method with cooling element
US5817049A (en) * 1994-05-09 1998-10-06 Somnus Medical Technologies, Inc. Method for treatment of airway obstructions
US5820580A (en) * 1996-02-23 1998-10-13 Somnus Medical Technologies, Inc. Method for ablating interior sections of the tongue
US5823197A (en) * 1994-06-24 1998-10-20 Somnus Medical Technologies, Inc. Method for internal ablation of turbinates
US5827277A (en) * 1994-06-24 1998-10-27 Somnus Medical Technologies, Inc. Minimally invasive apparatus for internal ablation of turbinates
US5836906A (en) * 1996-02-23 1998-11-17 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US5843021A (en) * 1994-05-09 1998-12-01 Somnus Medical Technologies, Inc. Cell necrosis apparatus
US5879349A (en) * 1996-02-23 1999-03-09 Somnus Medical Technologies, Inc. Apparatus for treatment of air way obstructions
US5913855A (en) 1995-08-15 1999-06-22 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5921954A (en) * 1996-07-10 1999-07-13 Mohr, Jr.; Lawrence G. Treating aneurysms by applying hardening/softening agents to hardenable/softenable substances
WO1999034743A1 (en) * 1998-01-09 1999-07-15 Radiotherapeutics Corporation Method and apparatus for monitoring solid tissue heating
US5925042A (en) 1995-08-15 1999-07-20 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5928229A (en) 1993-11-08 1999-07-27 Rita Medical Systems, Inc. Tumor ablation apparatus
US5944715A (en) 1996-06-20 1999-08-31 Gyrus Medical Limited Electrosurgical instrument
US5951547A (en) 1995-08-15 1999-09-14 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5971980A (en) * 1995-05-02 1999-10-26 Heart Rhythm Technologies, Inc. System for controlling the energy delivered to a patient for ablation
US5980517A (en) 1995-08-15 1999-11-09 Rita Medical Systems, Inc. Cell necrosis apparatus
US5995875A (en) * 1997-10-01 1999-11-30 United States Surgical Apparatus for thermal treatment of tissue
US6004319A (en) 1995-06-23 1999-12-21 Gyrus Medical Limited Electrosurgical instrument
US6009877A (en) * 1994-06-24 2000-01-04 Edwards; Stuart D. Method for treating a sphincter
US6013076A (en) 1996-01-09 2000-01-11 Gyrus Medical Limited Electrosurgical instrument
US6016452A (en) * 1996-03-19 2000-01-18 Kasevich; Raymond S. Dynamic heating method and radio frequency thermal treatment
US6015406A (en) 1996-01-09 2000-01-18 Gyrus Medical Limited Electrosurgical instrument
US6024740A (en) * 1997-07-08 2000-02-15 The Regents Of The University Of California Circumferential ablation device assembly
US6027501A (en) 1995-06-23 2000-02-22 Gyrus Medical Limited Electrosurgical instrument
US6044846A (en) * 1994-06-24 2000-04-04 Edwards; Stuart D. Method to treat esophageal sphincters
US6056744A (en) * 1994-06-24 2000-05-02 Conway Stuart Medical, Inc. Sphincter treatment apparatus
US6059780A (en) 1995-08-15 2000-05-09 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method with cooling element
US6063078A (en) * 1997-03-12 2000-05-16 Medtronic, Inc. Method and apparatus for tissue ablation
US6071280A (en) 1993-11-08 2000-06-06 Rita Medical Systems, Inc. Multiple electrode ablation apparatus
US6080150A (en) 1995-08-15 2000-06-27 Rita Medical Systems, Inc. Cell necrosis apparatus
US6090105A (en) 1995-08-15 2000-07-18 Rita Medical Systems, Inc. Multiple electrode ablation apparatus and method
US6090106A (en) 1996-01-09 2000-07-18 Gyrus Medical Limited Electrosurgical instrument
US6092528A (en) * 1994-06-24 2000-07-25 Edwards; Stuart D. Method to treat esophageal sphincters
US6106521A (en) * 1996-08-16 2000-08-22 United States Surgical Corporation Apparatus for thermal treatment of tissue
US6126657A (en) * 1996-02-23 2000-10-03 Somnus Medical Technologies, Inc. Apparatus for treatment of air way obstructions
US6132425A (en) 1995-08-15 2000-10-17 Gough; Edward J. Cell necrosis apparatus
US6152143A (en) * 1994-05-09 2000-11-28 Somnus Medical Technologies, Inc. Method for treatment of air way obstructions
US6164283A (en) * 1997-07-08 2000-12-26 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
US6210405B1 (en) 1996-06-20 2001-04-03 Gyrus Medical Limited Under water treatment
US6238389B1 (en) * 1997-09-30 2001-05-29 Boston Scientific Corporation Deflectable interstitial ablation device
US6245064B1 (en) 1997-07-08 2001-06-12 Atrionix, Inc. Circumferential ablation device assembly
US6258087B1 (en) 1998-02-19 2001-07-10 Curon Medical, Inc. Expandable electrode assemblies for forming lesions to treat dysfunction in sphincters and adjoining tissue regions
US6261286B1 (en) 1995-06-23 2001-07-17 Gyrus Medical Limited Electrosurgical generator and system
US6273886B1 (en) 1998-02-19 2001-08-14 Curon Medical, Inc. Integrated tissue heating and cooling apparatus
US6277114B1 (en) 1998-04-03 2001-08-21 Gyrus Medical Limited Electrode assembly for an electrosurical instrument
US6309386B1 (en) 1997-10-06 2001-10-30 Somnus Medical Technologies, Inc. Linear power control with PSK regulation
WO2001080756A1 (en) * 2000-04-27 2001-11-01 Medtronic, Inc. System and method for assessing transmurality of ablation lesions
US6325798B1 (en) 1998-02-19 2001-12-04 Curon Medical, Inc. Vacuum-assisted systems and methods for treating sphincters and adjoining tissue regions
US6338726B1 (en) 1997-02-06 2002-01-15 Vidacare, Inc. Treating urinary and other body strictures
US6355031B1 (en) 1998-02-19 2002-03-12 Curon Medical, Inc. Control systems for multiple electrode arrays to create lesions in tissue regions at or near a sphincter
US6358245B1 (en) 1998-02-19 2002-03-19 Curon Medical, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US6371926B1 (en) 1998-04-21 2002-04-16 Somnus Medical Technologies, Inc. Wire based temperature sensing electrodes
US6402741B1 (en) 1999-10-08 2002-06-11 Sherwood Services Ag Current and status monitor
US6402744B2 (en) 1998-02-19 2002-06-11 Curon Medical, Inc. Systems and methods for forming composite lesions to treat dysfunction in sphincters and adjoining tissue regions
US6405732B1 (en) 1994-06-24 2002-06-18 Curon Medical, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US6423058B1 (en) 1998-02-19 2002-07-23 Curon Medical, Inc. Assemblies to visualize and treat sphincters and adjoining tissue regions
US6428538B1 (en) 1995-10-20 2002-08-06 United States Surgical Corporation Apparatus and method for thermal treatment of body tissue
US6440128B1 (en) 1998-01-14 2002-08-27 Curon Medical, Inc. Actively cooled electrode assemblies for forming lesions to treat dysfunction in sphincters and adjoining tissue regions
US20020143324A1 (en) * 1998-02-19 2002-10-03 Curon Medical, Inc. Apparatus to detect and treat aberrant myoelectric activity
US6464697B1 (en) 1998-02-19 2002-10-15 Curon Medical, Inc. Stomach and adjoining tissue regions in the esophagus
US6471697B1 (en) 1997-05-09 2002-10-29 The Regents Of The University Of California Tissue ablation device and method
WO2002056782A3 (en) * 2001-01-19 2002-12-12 Celon Ag Medical Instruments Device for the electrothermal treatment of the human or animal body
US6500174B1 (en) 1997-07-08 2002-12-31 Atrionix, Inc. Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US6502576B1 (en) 1997-07-08 2003-01-07 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
US20030009165A1 (en) * 1998-01-14 2003-01-09 Curon Medical, Inc. GERD treatment apparatus and method
US6514249B1 (en) 1997-07-08 2003-02-04 Atrionix, Inc. Positioning system and method for orienting an ablation element within a pulmonary vein ostium
US20030060820A1 (en) * 1997-07-08 2003-03-27 Maguire Mark A. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6547776B1 (en) 2000-01-03 2003-04-15 Curon Medical, Inc. Systems and methods for treating tissue in the crura
US6558378B2 (en) 1998-05-05 2003-05-06 Cardiac Pacemakers, Inc. RF ablation system and method having automatic temperature control
US6562034B2 (en) 1998-02-19 2003-05-13 Curon Medical, Inc. Electrodes for creating lesions in tissue regions at or near a sphincter
US20030093070A1 (en) * 1998-05-08 2003-05-15 Bruno Strul Radio-frequency generator for powering an ablation device
US6565561B1 (en) 1996-06-20 2003-05-20 Cyrus Medical Limited Electrosurgical instrument
US6589238B2 (en) 1998-01-14 2003-07-08 Curon Medical, Inc. Sphincter treatment device
US6595989B1 (en) 1999-05-11 2003-07-22 Atrionix, Inc. Balloon anchor wire
US6599288B2 (en) 2000-05-16 2003-07-29 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US6607502B1 (en) 1998-11-25 2003-08-19 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US6613047B2 (en) 1994-06-24 2003-09-02 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US6652515B1 (en) 1997-07-08 2003-11-25 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US20040002740A1 (en) * 2002-05-08 2004-01-01 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US6689127B1 (en) 1995-08-15 2004-02-10 Rita Medical Systems Multiple antenna ablation apparatus and method with multiple sensor feedback
US20040055572A1 (en) * 2002-09-24 2004-03-25 Caterpillar Inc. Hydraulic pump circuit
US20040082947A1 (en) * 2002-10-25 2004-04-29 The Regents Of The University Of Michigan Ablation catheters
US20040098075A1 (en) * 2002-11-16 2004-05-20 The Regents Of The University Of California Cardiac stimulation system and method
US20040106896A1 (en) * 2002-11-29 2004-06-03 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US6749607B2 (en) 1998-03-06 2004-06-15 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US6752804B2 (en) 2000-12-28 2004-06-22 Cardiac Pacemakers, Inc. Ablation system and method having multiple-sensor electrodes to assist in assessment of electrode and sensor position and adjustment of energy levels
US6752805B2 (en) 2000-06-13 2004-06-22 Atrionix, Inc. Surgical ablation probe for forming a circumferential lesion
US6758830B1 (en) 1999-05-11 2004-07-06 Atrionix, Inc. Catheter positioning system
US20040147921A1 (en) * 1998-02-19 2004-07-29 Curon Medical, Inc. Sphincter treatment apparatus
US6780180B1 (en) 1995-06-23 2004-08-24 Gyrus Medical Limited Electrosurgical instrument
US6783523B2 (en) 1999-05-04 2004-08-31 Curon Medical, Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US6790207B2 (en) 1998-06-04 2004-09-14 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat disorders of the gastrointestinal tract
US6802841B2 (en) 1998-06-04 2004-10-12 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US6866663B2 (en) 1998-02-27 2005-03-15 Curon Medical, Inc. Method for treating a sphincter
US6869431B2 (en) 1997-07-08 2005-03-22 Atrionix, Inc. Medical device with sensor cooperating with expandable member
US20050149013A1 (en) * 2000-08-09 2005-07-07 Lee Bruce B. Gynecological ablation procedure and system
US20050154433A1 (en) * 2002-03-19 2005-07-14 Solarant Medical, Inc. Heating method for tissue contraction
US20050165393A1 (en) * 1996-12-31 2005-07-28 Eppstein Jonathan A. Microporation of tissue for delivery of bioactive agents
US6932804B2 (en) 2003-01-21 2005-08-23 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US6939346B2 (en) 1999-04-21 2005-09-06 Oratec Interventions, Inc. Method and apparatus for controlling a temperature-controlled probe
US6966908B2 (en) 1997-07-08 2005-11-22 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US20050267458A1 (en) * 2004-05-27 2005-12-01 Saurav Paul Side-port sheath for catheter placement and translation
US20050288662A1 (en) * 2004-06-23 2005-12-29 Uchida Andy H Electrosurgical generator
US20060004351A1 (en) * 1999-12-09 2006-01-05 Cryocath Technologies Inc. Catheter with cryogenic and electrical heating ablation
DE102004041681A1 (en) * 2004-08-20 2006-02-23 Celon Ag Medical Instruments An apparatus for electrosurgical sclerosing of body tissue
US7008417B2 (en) * 2002-04-22 2006-03-07 Medtronics, Inc. Detecting coagulum formation
US20060293649A1 (en) * 2005-06-22 2006-12-28 Lorang Douglas M Electrosurgical power control
US20070006215A1 (en) * 2005-07-01 2007-01-04 Gordon Epstein Anchored RF ablation device for the destruction of tissue masses
US20070016183A1 (en) * 2005-07-01 2007-01-18 Bruce Lee Radio frequency ablation device for the destruction of tissue masses
US20070055225A1 (en) * 2005-09-07 2007-03-08 Dodd Gerald D Iii Method and apparatus for electromagnetic ablation of biological tissue
US20070083193A1 (en) * 2005-08-22 2007-04-12 Werneth Randell L User interface for tissue ablation system
US20070149964A1 (en) * 2004-01-27 2007-06-28 Takashi Kawabata Ablation catheter
US20070203488A1 (en) * 2002-06-27 2007-08-30 Gyrus Medical Limited Electrosurgical system
US20080045940A1 (en) * 2000-08-09 2008-02-21 Halt Medical, Inc. Gynecological ablation system with laparoscopic and ultrasound imaging
US20080161803A1 (en) * 2002-10-25 2008-07-03 The Regents Of The University Of Michigan Ablation Catheters And Methods For Their Use
US20080255642A1 (en) * 2006-06-28 2008-10-16 Ardian, Inc. Methods and systems for thermally-induced renal neuromodulation
US20080275443A1 (en) * 2004-11-24 2008-11-06 Hakan Oral Atrial ablation catheter adapted for treatment of septal wall arrhythmogenic foci and method of use
US7462179B2 (en) 1998-01-14 2008-12-09 Respiratory Diagnostic, Inc. GERD treatment apparatus and method
US20090138011A1 (en) * 2007-03-13 2009-05-28 Gordon Epstein Intermittent ablation rf driving for moderating return electrode temperature
US20090171235A1 (en) * 2007-12-28 2009-07-02 Clint Schneider Method and apparatus for complex impedance compensation and for determining tissue morphology based on phase angle
US20090187182A1 (en) * 2007-11-14 2009-07-23 Gordon Epstein Rf ablation device with jam-preventing electrical coupling member
US20090248007A1 (en) * 2008-03-31 2009-10-01 Applied Medical Resources Corporation Electrosurgical system
WO2010000362A1 (en) * 2008-06-30 2010-01-07 Erbe Elektromedizin Gmbh Electrosurgical generator for the treatment of a biological tissue, method for regulating an output voltage of an electrosurgical generator, and corresponding use of the electrosurgical generator
US7647123B2 (en) 1996-08-13 2010-01-12 Oratec Interventions, Inc. Method for treating intervertebral discs
US7648499B2 (en) 2006-03-21 2010-01-19 Covidien Ag System and method for generating radio frequency energy
US7651493B2 (en) 2006-03-03 2010-01-26 Covidien Ag System and method for controlling electrosurgical snares
US7651492B2 (en) 2006-04-24 2010-01-26 Covidien Ag Arc based adaptive control system for an electrosurgical unit
US7722601B2 (en) 2003-05-01 2010-05-25 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US7731717B2 (en) 2006-08-08 2010-06-08 Covidien Ag System and method for controlling RF output during tissue sealing
US7749217B2 (en) 2002-05-06 2010-07-06 Covidien Ag Method and system for optically detecting blood and controlling a generator during electrosurgery
US7766905B2 (en) 2004-02-12 2010-08-03 Covidien Ag Method and system for continuity testing of medical electrodes
US7766693B2 (en) 2003-11-20 2010-08-03 Covidien Ag Connector systems for electrosurgical generator
US7780662B2 (en) 2004-03-02 2010-08-24 Covidien Ag Vessel sealing system using capacitive RF dielectric heating
US7794457B2 (en) 2006-09-28 2010-09-14 Covidien Ag Transformer for RF voltage sensing
US20100268208A1 (en) * 2009-04-17 2010-10-21 Kim Manwaring Surgical scalpel with inductively heated regions
US7824400B2 (en) 2002-12-10 2010-11-02 Covidien Ag Circuit for controlling arc energy from an electrosurgical generator
US7834484B2 (en) 2007-07-16 2010-11-16 Tyco Healthcare Group Lp Connection cable and method for activating a voltage-controlled generator
US7850685B2 (en) 2005-06-20 2010-12-14 Medtronic Ablation Frontiers Llc Ablation catheter
US7901400B2 (en) 1998-10-23 2011-03-08 Covidien Ag Method and system for controlling output of RF medical generator
US20110071468A1 (en) * 1998-06-04 2011-03-24 Mederi Therapeutics, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US20110071518A1 (en) * 2009-09-24 2011-03-24 Tyco Healthcare Group Lp System and Method for Multi-Pole Phase-Shifted Radio Frequency Application
US20110071516A1 (en) * 2009-09-24 2011-03-24 Tyco Healthcare Group Lp System and Method for Controlling Electrosurgical Output
US7927328B2 (en) 2006-01-24 2011-04-19 Covidien Ag System and method for closed loop monitoring of monopolar electrosurgical apparatus
US20110118727A1 (en) * 2005-12-06 2011-05-19 Fish Jeffrey M System and method for assessing the formation of a lesion in tissue
US7947039B2 (en) 2005-12-12 2011-05-24 Covidien Ag Laparoscopic apparatus for performing electrosurgical procedures
US7959627B2 (en) 2005-11-23 2011-06-14 Barrx Medical, Inc. Precision ablating device
US20110144524A1 (en) * 2005-12-06 2011-06-16 Fish Jeffrey M Graphical user interface for real-time rf lesion depth display
US7972328B2 (en) 2006-01-24 2011-07-05 Covidien Ag System and method for tissue sealing
US20110190759A1 (en) * 2000-05-18 2011-08-04 Mederi Therapeutics Inc. Graphical user interface for monitoring and controlling use of medical devices
US7993336B2 (en) 1999-11-16 2011-08-09 Barrx Medical, Inc. Methods and systems for determining physiologic characteristics for treatment of the esophagus
US7997278B2 (en) 2005-11-23 2011-08-16 Barrx Medical, Inc. Precision ablating method
US8012149B2 (en) 1999-11-16 2011-09-06 Barrx Medical, Inc. Methods and systems for determining physiologic characteristics for treatment of the esophagus
US20110224573A1 (en) * 2010-03-10 2011-09-15 Bar-Tal Meir Monitoring tissue temperature while using an irrigated catheter
US8025660B2 (en) 2004-10-13 2011-09-27 Covidien Ag Universal foot switch contact port
US8034049B2 (en) 2006-08-08 2011-10-11 Covidien Ag System and method for measuring initial tissue impedance
US8096961B2 (en) 2003-10-30 2012-01-17 Covidien Ag Switched resonant ultrasonic power amplifier system
US8105323B2 (en) 1998-10-23 2012-01-31 Covidien Ag Method and system for controlling output of RF medical generator
US8104956B2 (en) 2003-10-23 2012-01-31 Covidien Ag Thermocouple measurement circuit
US8147485B2 (en) 2006-01-24 2012-04-03 Covidien Ag System and method for tissue sealing
US8177781B2 (en) 2000-10-02 2012-05-15 Novasys Medical, Inc. Apparatus and methods for treating female urinary incontinence
US8187262B2 (en) 2006-01-24 2012-05-29 Covidien Ag Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling
US8192426B2 (en) 2004-01-09 2012-06-05 Tyco Healthcare Group Lp Devices and methods for treatment of luminal tissue
US8216223B2 (en) 2006-01-24 2012-07-10 Covidien Ag System and method for tissue sealing
US8216220B2 (en) 2007-09-07 2012-07-10 Tyco Healthcare Group Lp System and method for transmission of combined data stream
US8226639B2 (en) 2008-06-10 2012-07-24 Tyco Healthcare Group Lp System and method for output control of electrosurgical generator
US8251992B2 (en) 2007-07-06 2012-08-28 Tyco Healthcare Group Lp Method and apparatus for gastrointestinal tract ablation to achieve loss of persistent and/or recurrent excess body weight following a weight-loss operation
US8251991B2 (en) 2007-11-14 2012-08-28 Halt Medical Inc. Anchored RF ablation device for the destruction of tissue masses
EP2498509A2 (en) 2008-04-07 2012-09-12 Koss Corporation Wireless earphone that transitions between wireless networks
US20120239024A1 (en) * 2011-03-17 2012-09-20 Vivant Medical, Inc. Energy-Based Ablation Completion Algorithm
US8273084B2 (en) 2004-11-24 2012-09-25 Medtronic Ablation Frontiers Llc Atrial ablation catheter and method of use
US8273012B2 (en) 2007-07-30 2012-09-25 Tyco Healthcare Group, Lp Cleaning device and methods
US8287528B2 (en) 1998-10-23 2012-10-16 Covidien Ag Vessel sealing system
US8353908B2 (en) 1996-09-20 2013-01-15 Novasys Medical, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US8398631B2 (en) 1999-11-16 2013-03-19 Covidien Lp System and method of treating abnormal tissue in the human esophagus
US8403927B1 (en) 2012-04-05 2013-03-26 William Bruce Shingleton Vasectomy devices and methods
US8403925B2 (en) 2006-12-06 2013-03-26 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing lesions in tissue
US8412318B2 (en) 1996-05-06 2013-04-02 Novasys Medical, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US8439908B2 (en) 2007-07-06 2013-05-14 Covidien Lp Ablation in the gastrointestinal tract to achieve hemostasis and eradicate lesions with a propensity for bleeding
US8486061B2 (en) 2009-01-12 2013-07-16 Covidien Lp Imaginary impedance process monitoring and intelligent shut-off
US8486060B2 (en) 2006-09-18 2013-07-16 Cytyc Corporation Power ramping during RF ablation
US8486063B2 (en) 2004-10-14 2013-07-16 Medtronic Ablation Frontiers Llc Ablation catheter
US8506563B2 (en) 1996-04-12 2013-08-13 Cytyc Surgical Products Moisture transport system for contact electrocoagulation
US8512332B2 (en) 2007-09-21 2013-08-20 Covidien Lp Real-time arc control in electrosurgical generators
US8551082B2 (en) 1998-05-08 2013-10-08 Cytyc Surgical Products Radio-frequency generator for powering an ablation device
WO2013162884A1 (en) * 2012-04-26 2013-10-31 Medtronic Ablation Frontiers Llc System for detecting tissue contact during ablation
US8617151B2 (en) 2009-04-17 2013-12-31 Domain Surgical, Inc. System and method of controlling power delivery to a surgical instrument
US8617152B2 (en) 2004-11-15 2013-12-31 Medtronic Ablation Frontiers Llc Ablation system with feedback
US8641704B2 (en) 2007-05-11 2014-02-04 Medtronic Ablation Frontiers Llc Ablation therapy system and method for treating continuous atrial fibrillation
US8641711B2 (en) 2007-05-04 2014-02-04 Covidien Lp Method and apparatus for gastrointestinal tract ablation for treatment of obesity
US8646460B2 (en) 2007-07-30 2014-02-11 Covidien Lp Cleaning device and methods
US8663214B2 (en) 2006-01-24 2014-03-04 Covidien Ag Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm
US8685016B2 (en) 2006-01-24 2014-04-01 Covidien Ag System and method for tissue sealing
US8702694B2 (en) 2005-11-23 2014-04-22 Covidien Lp Auto-aligning ablating device and method of use
US8734438B2 (en) 2005-10-21 2014-05-27 Covidien Ag Circuit and method for reducing stored energy in an electrosurgical generator
US8753334B2 (en) 2006-05-10 2014-06-17 Covidien Ag System and method for reducing leakage current in an electrosurgical generator
US8777941B2 (en) 2007-05-10 2014-07-15 Covidien Lp Adjustable impedance electrosurgical electrodes
US8784338B2 (en) 2007-06-22 2014-07-22 Covidien Lp Electrical means to normalize ablational energy transmission to a luminal tissue surface of varying size
US8808161B2 (en) 2003-10-23 2014-08-19 Covidien Ag Redundant temperature monitoring in electrosurgical systems for safety mitigation
US8834461B2 (en) 2005-07-11 2014-09-16 Medtronic Ablation Frontiers Llc Low power tissue ablation system
US8894646B2 (en) 1998-02-19 2014-11-25 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US8906010B2 (en) 1998-02-19 2014-12-09 Mederi Therapeutics, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US8915909B2 (en) 2011-04-08 2014-12-23 Domain Surgical, Inc. Impedance matching circuit
US8932208B2 (en) 2005-05-26 2015-01-13 Maquet Cardiovascular Llc Apparatus and methods for performing minimally-invasive surgical procedures
US8932279B2 (en) 2011-04-08 2015-01-13 Domain Surgical, Inc. System and method for cooling of a heated surgical instrument and/or surgical site and treating tissue
US20150045976A1 (en) * 2013-08-09 2015-02-12 The Boeing Company Advanced energy monitoring and control in a complex system
US8998890B2 (en) 2005-12-06 2015-04-07 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
CN104582615A (en) * 2012-06-27 2015-04-29 麦迪尼治疗公司 Systems and methods for treating tissue with radio frequency energy
US9023031B2 (en) 1997-08-13 2015-05-05 Verathon Inc. Noninvasive devices, methods, and systems for modifying tissues
US9066720B2 (en) 2010-10-25 2015-06-30 Medtronic Ardian Luxembourg S.A.R.L. Devices, systems and methods for evaluation and feedback of neuromodulation treatment
US9078655B2 (en) 2009-04-17 2015-07-14 Domain Surgical, Inc. Heated balloon catheter
US9107666B2 (en) 2009-04-17 2015-08-18 Domain Surgical, Inc. Thermal resecting loop
US9131977B2 (en) 2009-04-17 2015-09-15 Domain Surgical, Inc. Layered ferromagnetic coated conductor thermal surgical tool
US9155583B2 (en) 1994-06-24 2015-10-13 Mederi Therapeutics, Inc. Systems and methods for monitoring and controlling use of medical devices
US9173586B2 (en) 2005-12-06 2015-11-03 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing coupling between an electrode and tissue
US9186200B2 (en) 2006-01-24 2015-11-17 Covidien Ag System and method for tissue sealing
US9186223B2 (en) 1999-09-08 2015-11-17 Mederi Therapeutics, Inc. Systems and methods for monitoring and controlling use of medical devices
US9204927B2 (en) 2009-05-13 2015-12-08 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for presenting information representative of lesion formation in tissue during an ablation procedure
USD748259S1 (en) 2014-12-29 2016-01-26 Applied Medical Resources Corporation Electrosurgical instrument
US9254163B2 (en) 2005-12-06 2016-02-09 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9265556B2 (en) 2009-04-17 2016-02-23 Domain Surgical, Inc. Thermally adjustable surgical tool, balloon catheters and sculpting of biologic materials
US9271782B2 (en) 2005-12-06 2016-03-01 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling of tissue ablation
US9292152B2 (en) 2009-09-22 2016-03-22 Mederi Therapeutics, Inc. Systems and methods for controlling use and operation of a family of different treatment devices
US9320563B2 (en) 2010-10-01 2016-04-26 Applied Medical Resources Corporation Electrosurgical instruments and connections thereto
US9474565B2 (en) 2009-09-22 2016-10-25 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9474564B2 (en) 2005-03-31 2016-10-25 Covidien Ag Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator
US20160338768A1 (en) * 2015-05-18 2016-11-24 Biosense Webster (Israel) Ltd. Catheter with coaxial thermocouple
US9526558B2 (en) 2011-09-13 2016-12-27 Domain Surgical, Inc. Sealing and/or cutting instrument
US9636165B2 (en) 2013-07-29 2017-05-02 Covidien Lp Systems and methods for measuring tissue impedance through an electrosurgical cable
US9750563B2 (en) 2009-09-22 2017-09-05 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9750570B2 (en) 2012-05-01 2017-09-05 Medtronic Ablation Frontiers Llc Systems and methods for detecting tissue contact during ablation
US9775664B2 (en) 2009-09-22 2017-10-03 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9872719B2 (en) 2013-07-24 2018-01-23 Covidien Lp Systems and methods for generating electrosurgical energy using a multistage power converter
US9980772B2 (en) 2011-02-28 2018-05-29 Biosense Webster (Israel) Ltd. Monitoring tissue temperature while using an irrigated catheter

Families Citing this family (60)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6142992A (en) * 1993-05-10 2000-11-07 Arthrocare Corporation Power supply for limiting power in electrosurgery
US6149620A (en) 1995-11-22 2000-11-21 Arthrocare Corporation System and methods for electrosurgical tissue treatment in the presence of electrically conductive fluid
US7270661B2 (en) * 1995-11-22 2007-09-18 Arthocare Corporation Electrosurgical apparatus and methods for treatment and removal of tissue
US5540681A (en) * 1992-04-10 1996-07-30 Medtronic Cardiorhythm Method and system for radiofrequency ablation of tissue
US5573533A (en) * 1992-04-10 1996-11-12 Medtronic Cardiorhythm Method and system for radiofrequency ablation of cardiac tissue
US5645082A (en) * 1993-01-29 1997-07-08 Cardima, Inc. Intravascular method and system for treating arrhythmia
US5699796A (en) * 1993-01-29 1997-12-23 Cardima, Inc. High resolution intravascular signal detection
US5372596A (en) * 1993-07-27 1994-12-13 Valleylab Inc. Apparatus for leakage control and method for its use
WO1995009561A1 (en) * 1993-10-01 1995-04-13 Target Therapeutics, Inc. Sheathed multipolar catheter and multipolar guidewire for sensing cardiac electrical activity
US6210403B1 (en) * 1993-10-07 2001-04-03 Sherwood Services Ag Automatic control for energy from an electrosurgical generator
US5422567A (en) * 1993-12-27 1995-06-06 Valleylab Inc. High frequency power measurement
WO1995021578A1 (en) * 1994-02-09 1995-08-17 Keravision, Inc. An electrosurgical procedure recurving the cornea
US5584830A (en) * 1994-03-30 1996-12-17 Medtronic Cardiorhythm Method and system for radiofrequency ablation of cardiac tissue
US6156031A (en) * 1995-08-09 2000-12-05 Eclipse Surgical Technologies Transmyocardial revascularization using radiofrequency energy
US6267757B1 (en) 1995-08-09 2001-07-31 Eclipse Surgical Technologies, Inc. Revascularization with RF ablation
US5817092A (en) * 1995-11-09 1998-10-06 Radio Therapeutics Corporation Apparatus, system and method for delivering radio frequency energy to a treatment site
DE19623840A1 (en) * 1996-06-14 1997-12-18 Berchtold Gmbh & Co Geb An electrosurgical high-frequency generator
US6033399A (en) * 1997-04-09 2000-03-07 Valleylab, Inc. Electrosurgical generator with adaptive power control
US5935124A (en) * 1997-12-02 1999-08-10 Cordis Webster, Inc. Tip electrode with multiple temperature sensors
US6047700A (en) * 1998-03-30 2000-04-11 Arthrocare Corporation Systems and methods for electrosurgical removal of calcified deposits
US6398779B1 (en) * 1998-10-23 2002-06-04 Sherwood Services Ag Vessel sealing system
US6796981B2 (en) 1999-09-30 2004-09-28 Sherwood Services Ag Vessel sealing system
US20040167508A1 (en) * 2002-02-11 2004-08-26 Robert Wham Vessel sealing system
US7250048B2 (en) * 2001-04-26 2007-07-31 Medtronic, Inc. Ablation system and method of use
US7959626B2 (en) 2001-04-26 2011-06-14 Medtronic, Inc. Transmural ablation systems and methods
US6630139B2 (en) * 2001-08-24 2003-10-07 Academia Sinica Fibrinogenolytic proteases with thrombolytic and antihypertensive activities: medical application and novel process of expression and production
US7008421B2 (en) * 2002-08-21 2006-03-07 Resect Medical, Inc. Apparatus and method for tissue resection
US7223264B2 (en) * 2002-08-21 2007-05-29 Resect Medical, Inc. Thermal coagulation of tissue during tissue resection
US7255694B2 (en) * 2002-12-10 2007-08-14 Sherwood Services Ag Variable output crest factor electrosurgical generator
US7297143B2 (en) * 2003-02-05 2007-11-20 Arthrocare Corporation Temperature indicating electrosurgical apparatus and methods
EP1651127B1 (en) 2003-07-16 2012-10-31 Arthrocare Corporation Rotary electrosurgical apparatus
US7300435B2 (en) * 2003-11-21 2007-11-27 Sherwood Services Ag Automatic control system for an electrosurgical generator
WO2006069313A1 (en) * 2004-12-20 2006-06-29 Vnus Medical Technologies, Inc. Systems and methods for treating a hollow anatomical structure
US7632267B2 (en) * 2005-07-06 2009-12-15 Arthrocare Corporation Fuse-electrode electrosurgical apparatus
US8636729B2 (en) 2005-07-21 2014-01-28 Covidien Lp Therapeutic system with energy application device and programmed power delivery
US20070106288A1 (en) * 2005-11-09 2007-05-10 Arthrocare Corporation Electrosurgical apparatus with fluid flow regulator
US20070161981A1 (en) * 2006-01-06 2007-07-12 Arthrocare Corporation Electrosurgical method and systems for treating glaucoma
US7691101B2 (en) * 2006-01-06 2010-04-06 Arthrocare Corporation Electrosurgical method and system for treating foot ulcer
US8876746B2 (en) 2006-01-06 2014-11-04 Arthrocare Corporation Electrosurgical system and method for treating chronic wound tissue
EP2020943B1 (en) 2006-05-30 2015-07-08 ArthroCare Corporation Hard tissue ablation system
GB2452103B (en) 2007-01-05 2011-08-31 Arthrocare Corp Electrosurgical system with suction control apparatus and system
US7862560B2 (en) * 2007-03-23 2011-01-04 Arthrocare Corporation Ablation apparatus having reduced nerve stimulation and related methods
US9358063B2 (en) * 2008-02-14 2016-06-07 Arthrocare Corporation Ablation performance indicator for electrosurgical devices
US8574187B2 (en) 2009-03-09 2013-11-05 Arthrocare Corporation System and method of an electrosurgical controller with output RF energy control
US8257350B2 (en) 2009-06-17 2012-09-04 Arthrocare Corporation Method and system of an electrosurgical controller with wave-shaping
US8932282B2 (en) 2009-08-03 2015-01-13 Covidien Lp Power level transitioning in a surgical instrument
US8377054B2 (en) * 2009-09-24 2013-02-19 Covidien Lp Automatic control circuit for use in an electrosurgical generator
US8372067B2 (en) 2009-12-09 2013-02-12 Arthrocare Corporation Electrosurgery irrigation primer systems and methods
US8747399B2 (en) 2010-04-06 2014-06-10 Arthrocare Corporation Method and system of reduction of low frequency muscle stimulation during electrosurgical procedures
US8685018B2 (en) 2010-10-15 2014-04-01 Arthrocare Corporation Electrosurgical wand and related method and system
USD658760S1 (en) 2010-10-15 2012-05-01 Arthrocare Corporation Wound care electrosurgical wand
US8568405B2 (en) 2010-10-15 2013-10-29 Arthrocare Corporation Electrosurgical wand and related method and system
US9131597B2 (en) 2011-02-02 2015-09-08 Arthrocare Corporation Electrosurgical system and method for treating hard body tissue
US9713489B2 (en) 2013-03-07 2017-07-25 Arthrocare Corporation Electrosurgical methods and systems
US9693818B2 (en) 2013-03-07 2017-07-04 Arthrocare Corporation Methods and systems related to electrosurgical wands
US9801678B2 (en) 2013-03-13 2017-10-31 Arthrocare Corporation Method and system of controlling conductive fluid flow during an electrosurgical procedure
US9216057B2 (en) 2013-03-15 2015-12-22 Kyphon Sarl Steerable catheter system and method of using a steerable catheter system to dissect and evacuate tissue
US9913679B2 (en) 2013-10-16 2018-03-13 Covidien Lp Electrosurgical systems and methods for monitoring power dosage
US20150282863A1 (en) * 2014-04-04 2015-10-08 Covidien Lp Systems and methods for calculating tissue impedance in electrosurgery
CN105310770B (en) * 2015-11-25 2017-10-31 清华大学深圳研究生院 Microwave tumor ablation instrument

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1935289A (en) * 1928-09-19 1933-11-14 Westinghouse Electric & Mfg Co Protective system
US3588710A (en) * 1968-08-05 1971-06-28 Westinghouse Electric Corp Digital phase detection circuitry
US4126137A (en) * 1977-01-21 1978-11-21 Minnesota Mining And Manufacturing Company Electrosurgical unit
US4352156A (en) * 1981-08-14 1982-09-28 Westinghouse Electric Corp. AC to AC Power converter with a controllable power factor
US4599553A (en) * 1985-02-28 1986-07-08 Westinghouse Electric Corp. Malfunction detector for static VAR controllers
US4658819A (en) * 1983-09-13 1987-04-21 Valleylab, Inc. Electrosurgical generator
DE3604823A1 (en) * 1986-02-15 1987-08-27 Flachenecker Gerhard High frequency generator with automatic power control for high frequency surgery
US4727874A (en) * 1984-09-10 1988-03-01 C. R. Bard, Inc. Electrosurgical generator with high-frequency pulse width modulated feedback power control
US4862889A (en) * 1987-04-10 1989-09-05 Siemens Aktiengesellschaft Monitoring circuit for an RF surgical apparatus

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3480462D1 (en) * 1983-09-13 1989-12-21 Valleylab Inc Electrosurgical generator
GB8401887D0 (en) * 1984-01-25 1984-02-29 Matburn Holdings Ltd Electrosurgical unit
GB2213381B (en) * 1987-12-12 1992-06-03 Univ Wales Medicine Surgical diathermy instruments
US4961047A (en) * 1988-11-10 1990-10-02 Smiths Industries Public Limited Company Electrical power control apparatus and methods
WO1993008756A1 (en) * 1991-11-08 1993-05-13 Ep Technologies, Inc. Radiofrequency ablation with phase sensitive power detection

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1935289A (en) * 1928-09-19 1933-11-14 Westinghouse Electric & Mfg Co Protective system
US3588710A (en) * 1968-08-05 1971-06-28 Westinghouse Electric Corp Digital phase detection circuitry
US4126137A (en) * 1977-01-21 1978-11-21 Minnesota Mining And Manufacturing Company Electrosurgical unit
US4352156A (en) * 1981-08-14 1982-09-28 Westinghouse Electric Corp. AC to AC Power converter with a controllable power factor
US4658819A (en) * 1983-09-13 1987-04-21 Valleylab, Inc. Electrosurgical generator
US4727874A (en) * 1984-09-10 1988-03-01 C. R. Bard, Inc. Electrosurgical generator with high-frequency pulse width modulated feedback power control
US4599553A (en) * 1985-02-28 1986-07-08 Westinghouse Electric Corp. Malfunction detector for static VAR controllers
DE3604823A1 (en) * 1986-02-15 1987-08-27 Flachenecker Gerhard High frequency generator with automatic power control for high frequency surgery
US4862889A (en) * 1987-04-10 1989-09-05 Siemens Aktiengesellschaft Monitoring circuit for an RF surgical apparatus

Cited By (481)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5722975A (en) * 1991-11-08 1998-03-03 E.P. Technologies Inc. Systems for radiofrequency ablation with phase sensitive power detection and control
US5718702A (en) * 1992-08-12 1998-02-17 Somnus Medical Technologies, Inc. Uvula, tonsil, adenoid and sinus tissue treatment device and method
US6071280A (en) 1993-11-08 2000-06-06 Rita Medical Systems, Inc. Multiple electrode ablation apparatus
US5928229A (en) 1993-11-08 1999-07-27 Rita Medical Systems, Inc. Tumor ablation apparatus
US5683384A (en) * 1993-11-08 1997-11-04 Zomed Multiple antenna ablation apparatus
US6416491B1 (en) 1994-05-09 2002-07-09 Stuart D. Edwards Cell necrosis apparatus
US5817049A (en) * 1994-05-09 1998-10-06 Somnus Medical Technologies, Inc. Method for treatment of airway obstructions
US5843021A (en) * 1994-05-09 1998-12-01 Somnus Medical Technologies, Inc. Cell necrosis apparatus
US5730719A (en) * 1994-05-09 1998-03-24 Somnus Medical Technologies, Inc. Method and apparatus for cosmetically remodeling a body structure
US6179803B1 (en) 1994-05-09 2001-01-30 Somnus Medical Technologies, Inc. Cell necrosis apparatus
US5743870A (en) * 1994-05-09 1998-04-28 Somnus Medical Technologies, Inc. Ablation apparatus and system for removal of soft palate tissue
US6152143A (en) * 1994-05-09 2000-11-28 Somnus Medical Technologies, Inc. Method for treatment of air way obstructions
US6009877A (en) * 1994-06-24 2000-01-04 Edwards; Stuart D. Method for treating a sphincter
US6517535B2 (en) 1994-06-24 2003-02-11 Gyrus Ent L.L.C. Apparatus for ablating turbinates
US6056744A (en) * 1994-06-24 2000-05-02 Conway Stuart Medical, Inc. Sphincter treatment apparatus
US20070032788A1 (en) * 1994-06-24 2007-02-08 Curon Medical, Inc. Sphincter treatment apparatus
US6405732B1 (en) 1994-06-24 2002-06-18 Curon Medical, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US5800429A (en) * 1994-06-24 1998-09-01 Somnus Medical Technologies, Inc. Noninvasive apparatus for ablating turbinates
US9155583B2 (en) 1994-06-24 2015-10-13 Mederi Therapeutics, Inc. Systems and methods for monitoring and controlling use of medical devices
US7125407B2 (en) 1994-06-24 2006-10-24 Curon Medical, Inc. Sphincter treatment apparatus
US6092528A (en) * 1994-06-24 2000-07-25 Edwards; Stuart D. Method to treat esophageal sphincters
US5823197A (en) * 1994-06-24 1998-10-20 Somnus Medical Technologies, Inc. Method for internal ablation of turbinates
US5827277A (en) * 1994-06-24 1998-10-27 Somnus Medical Technologies, Inc. Minimally invasive apparatus for internal ablation of turbinates
US6613047B2 (en) 1994-06-24 2003-09-02 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US6673070B2 (en) 1994-06-24 2004-01-06 Curon Medical, Inc. Sphincter treatment apparatus
US6254598B1 (en) 1994-06-24 2001-07-03 Curon Medical, Inc. Sphincter treatment apparatus
US5746224A (en) * 1994-06-24 1998-05-05 Somnus Medical Technologies, Inc. Method for ablating turbinates
US6044846A (en) * 1994-06-24 2000-04-04 Edwards; Stuart D. Method to treat esophageal sphincters
US5769847A (en) * 1994-06-27 1998-06-23 Ep Technologies, Inc. Systems and methods for controlling tissue ablation using multiple temperature sensing elements
US5606974A (en) * 1995-05-02 1997-03-04 Heart Rhythm Technologies, Inc. Catheter having ultrasonic device
US5971980A (en) * 1995-05-02 1999-10-26 Heart Rhythm Technologies, Inc. System for controlling the energy delivered to a patient for ablation
US6364877B1 (en) 1995-06-23 2002-04-02 Gyrus Medical Limited Electrosurgical generator and system
US6261286B1 (en) 1995-06-23 2001-07-17 Gyrus Medical Limited Electrosurgical generator and system
US6416509B1 (en) 1995-06-23 2002-07-09 Gyrus Medical Limited Electrosurgical generator and system
US6174308B1 (en) 1995-06-23 2001-01-16 Gyrus Medical Limited Electrosurgical instrument
US6056746A (en) 1995-06-23 2000-05-02 Gyrus Medical Limited Electrosurgical instrument
US6004319A (en) 1995-06-23 1999-12-21 Gyrus Medical Limited Electrosurgical instrument
US6306134B1 (en) 1995-06-23 2001-10-23 Gyrus Medical Limited Electrosurgical generator and system
US6027501A (en) 1995-06-23 2000-02-22 Gyrus Medical Limited Electrosurgical instrument
US6780180B1 (en) 1995-06-23 2004-08-24 Gyrus Medical Limited Electrosurgical instrument
US5913855A (en) 1995-08-15 1999-06-22 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US20040260282A1 (en) * 1995-08-15 2004-12-23 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method with multiple sensor feedback
US6689127B1 (en) 1995-08-15 2004-02-10 Rita Medical Systems Multiple antenna ablation apparatus and method with multiple sensor feedback
US8734439B2 (en) 1995-08-15 2014-05-27 Angiodynamics, Inc Ablation apparatus and method
US5672174A (en) * 1995-08-15 1997-09-30 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5980517A (en) 1995-08-15 1999-11-09 Rita Medical Systems, Inc. Cell necrosis apparatus
US6059780A (en) 1995-08-15 2000-05-09 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method with cooling element
US5672173A (en) * 1995-08-15 1997-09-30 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5728143A (en) * 1995-08-15 1998-03-17 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US6080150A (en) 1995-08-15 2000-06-27 Rita Medical Systems, Inc. Cell necrosis apparatus
US5735847A (en) * 1995-08-15 1998-04-07 Zomed International, Inc. Multiple antenna ablation apparatus and method with cooling element
US6090105A (en) 1995-08-15 2000-07-18 Rita Medical Systems, Inc. Multiple electrode ablation apparatus and method
US5810804A (en) * 1995-08-15 1998-09-22 Rita Medical Systems Multiple antenna ablation apparatus and method with cooling element
US5925042A (en) 1995-08-15 1999-07-20 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5782827A (en) * 1995-08-15 1998-07-21 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method with multiple sensor feedback
US5951547A (en) 1995-08-15 1999-09-14 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US6132425A (en) 1995-08-15 2000-10-17 Gough; Edward J. Cell necrosis apparatus
US6428538B1 (en) 1995-10-20 2002-08-06 United States Surgical Corporation Apparatus and method for thermal treatment of body tissue
US6090106A (en) 1996-01-09 2000-07-18 Gyrus Medical Limited Electrosurgical instrument
US6013076A (en) 1996-01-09 2000-01-11 Gyrus Medical Limited Electrosurgical instrument
US6234178B1 (en) 1996-01-09 2001-05-22 Gyrus Medical Limited Electrosurgical instrument
US6015406A (en) 1996-01-09 2000-01-18 Gyrus Medical Limited Electrosurgical instrument
US5836906A (en) * 1996-02-23 1998-11-17 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US6126657A (en) * 1996-02-23 2000-10-03 Somnus Medical Technologies, Inc. Apparatus for treatment of air way obstructions
US5738114A (en) * 1996-02-23 1998-04-14 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US5879349A (en) * 1996-02-23 1999-03-09 Somnus Medical Technologies, Inc. Apparatus for treatment of air way obstructions
US5728094A (en) * 1996-02-23 1998-03-17 Somnus Medical Technologies, Inc. Method and apparatus for treatment of air way obstructions
US5820580A (en) * 1996-02-23 1998-10-13 Somnus Medical Technologies, Inc. Method for ablating interior sections of the tongue
US5800379A (en) * 1996-02-23 1998-09-01 Sommus Medical Technologies, Inc. Method for ablating interior sections of the tongue
US6016452A (en) * 1996-03-19 2000-01-18 Kasevich; Raymond S. Dynamic heating method and radio frequency thermal treatment
US9247989B2 (en) 1996-04-12 2016-02-02 Cytyc Surgical Products Moisture transport system for contact electrocoagulation
US8998898B2 (en) 1996-04-12 2015-04-07 Cytyc Surgical Products Moisture transport system for contact electrocoagulation
US9095348B2 (en) 1996-04-12 2015-08-04 Cytyc Surgical Products Moisture transport system for contact electrocoagulation
US8506563B2 (en) 1996-04-12 2013-08-13 Cytyc Surgical Products Moisture transport system for contact electrocoagulation
US8412318B2 (en) 1996-05-06 2013-04-02 Novasys Medical, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US5743904A (en) * 1996-05-06 1998-04-28 Somnus Medical Technologies, Inc. Precision placement of ablation apparatus
US6482202B1 (en) 1996-06-20 2002-11-19 Gyrus Medical Limited Under water treatment
US6565561B1 (en) 1996-06-20 2003-05-20 Cyrus Medical Limited Electrosurgical instrument
US6210405B1 (en) 1996-06-20 2001-04-03 Gyrus Medical Limited Under water treatment
US5944715A (en) 1996-06-20 1999-08-31 Gyrus Medical Limited Electrosurgical instrument
US5921954A (en) * 1996-07-10 1999-07-13 Mohr, Jr.; Lawrence G. Treating aneurysms by applying hardening/softening agents to hardenable/softenable substances
US7647123B2 (en) 1996-08-13 2010-01-12 Oratec Interventions, Inc. Method for treating intervertebral discs
US8226697B2 (en) 1996-08-13 2012-07-24 Neurotherm, Inc. Method for treating intervertebral disc
US8187312B2 (en) 1996-08-13 2012-05-29 Neurotherm, Inc. Method for treating intervertebral disc
US6106521A (en) * 1996-08-16 2000-08-22 United States Surgical Corporation Apparatus for thermal treatment of tissue
US8740846B2 (en) 1996-09-20 2014-06-03 Verathon, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US8353908B2 (en) 1996-09-20 2013-01-15 Novasys Medical, Inc. Treatment of tissue in sphincters, sinuses, and orifices
US7507234B2 (en) 1996-10-11 2009-03-24 BÂRRX Medical, Inc. Method for cryogenic tissue ablation
US20050165393A1 (en) * 1996-12-31 2005-07-28 Eppstein Jonathan A. Microporation of tissue for delivery of bioactive agents
US9579380B2 (en) * 1996-12-31 2017-02-28 Ntt Denko Corporation Microporation of tissue for delivery of bioactive agents
US6338726B1 (en) 1997-02-06 2002-01-15 Vidacare, Inc. Treating urinary and other body strictures
US6063078A (en) * 1997-03-12 2000-05-16 Medtronic, Inc. Method and apparatus for tissue ablation
US7993337B2 (en) 1997-05-09 2011-08-09 The Regents Of The University Of California Circumferential ablation device assembly
US6471697B1 (en) 1997-05-09 2002-10-29 The Regents Of The University Of California Tissue ablation device and method
US6254599B1 (en) 1997-05-09 2001-07-03 Atrionix, Inc. Circumferential ablation device assembly
US20060084966A1 (en) * 1997-07-08 2006-04-20 Maguire Mark A Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6500174B1 (en) 1997-07-08 2002-12-31 Atrionix, Inc. Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US6502576B1 (en) 1997-07-08 2003-01-07 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
US6964660B2 (en) 1997-07-08 2005-11-15 Atrionix, Inc. Tissue ablation device assembly and method of electrically isolating a pulmonary vein ostium from an atrial wall
US6514249B1 (en) 1997-07-08 2003-02-04 Atrionix, Inc. Positioning system and method for orienting an ablation element within a pulmonary vein ostium
US6997925B2 (en) 1997-07-08 2006-02-14 Atrionx, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US20030060820A1 (en) * 1997-07-08 2003-03-27 Maguire Mark A. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6245064B1 (en) 1997-07-08 2001-06-12 Atrionix, Inc. Circumferential ablation device assembly
US6954977B2 (en) 1997-07-08 2005-10-18 Maguire Mark A Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US6869431B2 (en) 1997-07-08 2005-03-22 Atrionix, Inc. Medical device with sensor cooperating with expandable member
US6652515B1 (en) 1997-07-08 2003-11-25 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US20050165391A1 (en) * 1997-07-08 2005-07-28 Maguire Mark A. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6164283A (en) * 1997-07-08 2000-12-26 The Regents Of The University Of California Device and method for forming a circumferential conduction block in a pulmonary vein
US6966908B2 (en) 1997-07-08 2005-11-22 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US6024740A (en) * 1997-07-08 2000-02-15 The Regents Of The University Of California Circumferential ablation device assembly
US6758847B2 (en) 1997-07-08 2004-07-06 Atrionix, Inc. Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US7340307B2 (en) 1997-07-08 2008-03-04 Atrionix, Inc. Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall
US9023031B2 (en) 1997-08-13 2015-05-05 Verathon Inc. Noninvasive devices, methods, and systems for modifying tissues
US6238389B1 (en) * 1997-09-30 2001-05-29 Boston Scientific Corporation Deflectable interstitial ablation device
US6352534B1 (en) * 1997-09-30 2002-03-05 Boston Scientific Corporation Deflectable interstitial ablation device
US6482203B2 (en) 1997-09-30 2002-11-19 Scimed Life Systems, Inc. Deflectable interstitial ablation device
US7909821B2 (en) 1997-09-30 2011-03-22 Boston Scientific Scimed, Inc. Deflectable interstitial ablation device
US5995875A (en) * 1997-10-01 1999-11-30 United States Surgical Apparatus for thermal treatment of tissue
US6309386B1 (en) 1997-10-06 2001-10-30 Somnus Medical Technologies, Inc. Linear power control with PSK regulation
US6080149A (en) * 1998-01-09 2000-06-27 Radiotherapeutics, Corporation Method and apparatus for monitoring solid tissue heating
WO1999034743A1 (en) * 1998-01-09 1999-07-15 Radiotherapeutics Corporation Method and apparatus for monitoring solid tissue heating
US20030195509A1 (en) * 1998-01-14 2003-10-16 Curon Medical, Inc. GERB treatment apparatus and method
US20060041256A1 (en) * 1998-01-14 2006-02-23 Curon Medical, Inc. GERD treatment apparatus and method
US6589238B2 (en) 1998-01-14 2003-07-08 Curon Medical, Inc. Sphincter treatment device
US6971395B2 (en) 1998-01-14 2005-12-06 Curon Medical, Inc. Sphincter treatment method
US7462179B2 (en) 1998-01-14 2008-12-09 Respiratory Diagnostic, Inc. GERD treatment apparatus and method
US6846312B2 (en) 1998-01-14 2005-01-25 Curon Medical, Inc. GERD treatment apparatus and method
US8313484B2 (en) 1998-01-14 2012-11-20 Mederi Therapeutics Inc. GERD treatment apparatus and method
US6440128B1 (en) 1998-01-14 2002-08-27 Curon Medical, Inc. Actively cooled electrode assemblies for forming lesions to treat dysfunction in sphincters and adjoining tissue regions
US20030009165A1 (en) * 1998-01-14 2003-01-09 Curon Medical, Inc. GERD treatment apparatus and method
US7165551B2 (en) 1998-02-19 2007-01-23 Curon Medical, Inc. Apparatus to detect and treat aberrant myoelectric activity
US8454595B2 (en) 1998-02-19 2013-06-04 Mederi Therapeutics, Inc Sphincter treatment apparatus
US20090254079A1 (en) * 1998-02-19 2009-10-08 Mederi Therapeutics, Inc. Methods for treating the cardia of the stomach
US20040147921A1 (en) * 1998-02-19 2004-07-29 Curon Medical, Inc. Sphincter treatment apparatus
US6402744B2 (en) 1998-02-19 2002-06-11 Curon Medical, Inc. Systems and methods for forming composite lesions to treat dysfunction in sphincters and adjoining tissue regions
US20060015162A1 (en) * 1998-02-19 2006-01-19 Curon Medical, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US7585296B2 (en) 1998-02-19 2009-09-08 Mederi Therapeutics, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US6355031B1 (en) 1998-02-19 2002-03-12 Curon Medical, Inc. Control systems for multiple electrode arrays to create lesions in tissue regions at or near a sphincter
US7122031B2 (en) 1998-02-19 2006-10-17 Curon Medical, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US6464697B1 (en) 1998-02-19 2002-10-15 Curon Medical, Inc. Stomach and adjoining tissue regions in the esophagus
US9351787B2 (en) 1998-02-19 2016-05-31 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US7648500B2 (en) 1998-02-19 2010-01-19 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US6562034B2 (en) 1998-02-19 2003-05-13 Curon Medical, Inc. Electrodes for creating lesions in tissue regions at or near a sphincter
US6974456B2 (en) 1998-02-19 2005-12-13 Curon Medical, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US6258087B1 (en) 1998-02-19 2001-07-10 Curon Medical, Inc. Expandable electrode assemblies for forming lesions to treat dysfunction in sphincters and adjoining tissue regions
US20100087809A1 (en) * 1998-02-19 2010-04-08 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US6712074B2 (en) 1998-02-19 2004-03-30 Curon Medical, Inc. Systems and methods for forming composite lesions to treat dysfunction in sphincters and adjoining tissue regions
US6423058B1 (en) 1998-02-19 2002-07-23 Curon Medical, Inc. Assemblies to visualize and treat sphincters and adjoining tissue regions
US6872206B2 (en) 1998-02-19 2005-03-29 Curon Medical, Inc. Methods for treating the cardia of the stomach
US6358245B1 (en) 1998-02-19 2002-03-19 Curon Medical, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US8152803B2 (en) 1998-02-19 2012-04-10 Mederi Therapeutics, Inc. Apparatus to detect and treat aberrant myoelectric activity
US8894646B2 (en) 1998-02-19 2014-11-25 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US8790339B2 (en) 1998-02-19 2014-07-29 Mederi Therapeutics Inc. Apparatus to detect and treat aberrant myoelectric activity
US6273886B1 (en) 1998-02-19 2001-08-14 Curon Medical, Inc. Integrated tissue heating and cooling apparatus
US9539052B2 (en) 1998-02-19 2017-01-10 Mederi Therapeutics, Inc. Sphincter treatment apparatus
US6712814B2 (en) 1998-02-19 2004-03-30 Curon Medical, Inc. Method for treating a sphincter
US8870862B2 (en) 1998-02-19 2014-10-28 Mederi Therapeutics, Inc. Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors
US20050245926A1 (en) * 1998-02-19 2005-11-03 Curon Medical, Inc. Sphincter treatment apparatus
US6325798B1 (en) 1998-02-19 2001-12-04 Curon Medical, Inc. Vacuum-assisted systems and methods for treating sphincters and adjoining tissue regions
US8906010B2 (en) 1998-02-19 2014-12-09 Mederi Therapeutics, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US20020143324A1 (en) * 1998-02-19 2002-10-03 Curon Medical, Inc. Apparatus to detect and treat aberrant myoelectric activity
US8518032B2 (en) 1998-02-27 2013-08-27 Mederi Therapeutics Inc. Method for treating a sphincter
US7449020B2 (en) 1998-02-27 2008-11-11 Curon Medical, Inc. Method for treating a sphincter
US20090076438A1 (en) * 1998-02-27 2009-03-19 Respiratory Diagnostic, Inc. Method for treating a sphincter
US6866663B2 (en) 1998-02-27 2005-03-15 Curon Medical, Inc. Method for treating a sphincter
US20110098702A1 (en) * 1998-03-06 2011-04-28 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US20040204708A1 (en) * 1998-03-06 2004-10-14 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US20070093809A1 (en) * 1998-03-06 2007-04-26 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US6749607B2 (en) 1998-03-06 2004-06-15 Curon Medical, Inc. Apparatus to treat esophageal sphincters
US6277114B1 (en) 1998-04-03 2001-08-21 Gyrus Medical Limited Electrode assembly for an electrosurical instrument
US6371926B1 (en) 1998-04-21 2002-04-16 Somnus Medical Technologies, Inc. Wire based temperature sensing electrodes
US20030195501A1 (en) * 1998-05-05 2003-10-16 Sherman Marshall L. RF ablation system and method having automatic temperature control
US6558378B2 (en) 1998-05-05 2003-05-06 Cardiac Pacemakers, Inc. RF ablation system and method having automatic temperature control
US8551082B2 (en) 1998-05-08 2013-10-08 Cytyc Surgical Products Radio-frequency generator for powering an ablation device
US20060025758A1 (en) * 1998-05-08 2006-02-02 Bruno Strul Radio-frequency generator for powering an ablation device
US7074217B2 (en) 1998-05-08 2006-07-11 Cytyc Surgical Products Radio-frequency generator for powering an ablation device
US9554853B2 (en) 1998-05-08 2017-01-31 Hologic, Inc. Radio-frequency generator for powering an ablation device
US20050245921A1 (en) * 1998-05-08 2005-11-03 Bruno Strul Radio-frequency generator for powering an ablation device
US20030093070A1 (en) * 1998-05-08 2003-05-15 Bruno Strul Radio-frequency generator for powering an ablation device
US7407502B2 (en) 1998-05-08 2008-08-05 Cytyc Corporation Radio-frequency generator for powering an ablation device
US7717909B2 (en) 1998-05-08 2010-05-18 Cytyc Surgical Products Radio-frequency generator for powering an ablation device
US6802841B2 (en) 1998-06-04 2004-10-12 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US20050010162A1 (en) * 1998-06-04 2005-01-13 Curon Medical, Inc. Systems methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US7458378B2 (en) 1998-06-04 2008-12-02 Respiratory Diagnostics, Inc. Systems methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US20050010171A1 (en) * 1998-06-04 2005-01-13 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat disorders of the gastrointestinal tract
US20110071468A1 (en) * 1998-06-04 2011-03-24 Mederi Therapeutics, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US8161976B2 (en) 1998-06-04 2012-04-24 Mederi Therapeutics, Inc. Systems and methods for applying a selected treatment agent into contact with tissue
US20090082721A1 (en) * 1998-06-04 2009-03-26 Respiratory Diagnostics, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat sphincter dysfunction
US7293563B2 (en) 1998-06-04 2007-11-13 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat disorders of the gastrointestinal tract
US6790207B2 (en) 1998-06-04 2004-09-14 Curon Medical, Inc. Systems and methods for applying a selected treatment agent into contact with tissue to treat disorders of the gastrointestinal tract
US8105323B2 (en) 1998-10-23 2012-01-31 Covidien Ag Method and system for controlling output of RF medical generator
US8287528B2 (en) 1998-10-23 2012-10-16 Covidien Ag Vessel sealing system
US9113900B2 (en) 1998-10-23 2015-08-25 Covidien Ag Method and system for controlling output of RF medical generator
US7901400B2 (en) 1998-10-23 2011-03-08 Covidien Ag Method and system for controlling output of RF medical generator
US9168089B2 (en) 1998-10-23 2015-10-27 Covidien Ag Method and system for controlling output of RF medical generator
US6607502B1 (en) 1998-11-25 2003-08-19 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US7241295B2 (en) 1999-03-19 2007-07-10 Astrionix Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member
US6939346B2 (en) 1999-04-21 2005-09-06 Oratec Interventions, Inc. Method and apparatus for controlling a temperature-controlled probe
US9198705B2 (en) 1999-05-04 2015-12-01 Mederi Therapeutics, Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US6783523B2 (en) 1999-05-04 2004-08-31 Curon Medical, Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US8888774B2 (en) 1999-05-04 2014-11-18 Mederi Therapeutics, Inc. Methods for treating the cardia of the stomach
US20050033271A1 (en) * 1999-05-04 2005-02-10 Curon Medical, Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US9844406B2 (en) 1999-05-04 2017-12-19 Mederi Therapeutics, Inc. Graphical user interface for association with an electrode structure deployed in contact with a tissue region
US20070294108A1 (en) * 1999-05-04 2007-12-20 Curon Medical, Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US8257346B2 (en) 1999-05-04 2012-09-04 Mederi Therapeutics Inc. Unified systems and methods for controlling use and operation of a family of different treatment devices
US7731681B2 (en) 1999-05-11 2010-06-08 Atrionix, Inc. Catheter positioning system
US6758830B1 (en) 1999-05-11 2004-07-06 Atrionix, Inc. Catheter positioning system
US6595989B1 (en) 1999-05-11 2003-07-22 Atrionix, Inc. Balloon anchor wire
US6811544B2 (en) 1999-05-11 2004-11-02 Alan K. Schaer Catheter positioning system
US7881807B2 (en) 1999-05-11 2011-02-01 Schaer Alan K Balloon anchor wire
US20040181188A1 (en) * 1999-05-11 2004-09-16 Schaer Alan K. Catheter positioning system
US9925000B2 (en) 1999-09-08 2018-03-27 Mederi Therapeutics, Inc. Systems and methods for monitoring and controlling use of medical devices
US9186223B2 (en) 1999-09-08 2015-11-17 Mederi Therapeutics, Inc. Systems and methods for monitoring and controlling use of medical devices
US9750559B2 (en) 1999-09-08 2017-09-05 Mederi Therapeutics Inc System and methods for monitoring and controlling use of medical devices
US6402741B1 (en) 1999-10-08 2002-06-11 Sherwood Services Ag Current and status monitor
US9555222B2 (en) 1999-11-16 2017-01-31 Covidien Lp Methods and systems for determining physiologic characteristics for treatment of the esophagus
US8876818B2 (en) 1999-11-16 2014-11-04 Covidien Lp Methods and systems for determining physiologic characteristics for treatment of the esophagus
US8377055B2 (en) 1999-11-16 2013-02-19 Covidien Lp Methods and systems for determining physiologic characteristics for treatment of the esophagus
US8398631B2 (en) 1999-11-16 2013-03-19 Covidien Lp System and method of treating abnormal tissue in the human esophagus
US9597147B2 (en) 1999-11-16 2017-03-21 Covidien Lp Methods and systems for treatment of tissue in a body lumen
US8012149B2 (en) 1999-11-16 2011-09-06 Barrx Medical, Inc. Methods and systems for determining physiologic characteristics for treatment of the esophagus
US9039699B2 (en) 1999-11-16 2015-05-26 Covidien Lp Methods and systems for treatment of tissue in a body lumen
US7993336B2 (en) 1999-11-16 2011-08-09 Barrx Medical, Inc. Methods and systems for determining physiologic characteristics for treatment of the esophagus
US20070299432A1 (en) * 1999-12-09 2007-12-27 Cryocath Technologies Inc. Catheter with cryogenic and electrical heating ablation
US7896870B2 (en) * 1999-12-09 2011-03-01 Medtronic Cryocath Lp Catheter with cryogenic and electrical heating ablation
US7465300B2 (en) 1999-12-09 2008-12-16 Cryocath Technologies Inc. Catheter with cryogenic and electrical heating ablation
US8083732B2 (en) 1999-12-09 2011-12-27 Medtronic Cryocath Lp Catheter with cryogenic and electrical heating ablation
US7097641B1 (en) 1999-12-09 2006-08-29 Cryocath Technologies Inc. Catheter with cryogenic and heating ablation
US20080114345A1 (en) * 1999-12-09 2008-05-15 Cryocath Technologies Inc. Catheter with cryogenic and electrical heating ablation
US8287526B2 (en) 1999-12-09 2012-10-16 Medtronic Cryocath Lp Method of simultaneously freezing and heating tissue for ablation
US7951140B2 (en) 1999-12-09 2011-05-31 Medtronic Cryocath Lp Catheter with cryogenic and electrical heating ablation
US20110196359A1 (en) * 1999-12-09 2011-08-11 Medtronic Cryocath Lp Catheter with cryogenic and electrical heating ablation
US20060004351A1 (en) * 1999-12-09 2006-01-05 Cryocath Technologies Inc. Catheter with cryogenic and electrical heating ablation
US6547776B1 (en) 2000-01-03 2003-04-15 Curon Medical, Inc. Systems and methods for treating tissue in the crura
EP1818021A1 (en) * 2000-04-27 2007-08-15 Medtronic Inc. System for assessing transmurality of ablation lesions
WO2001082811A1 (en) * 2000-04-27 2001-11-08 Medtronic, Inc. System and method for assessing transmurality of ablation lesions
US6584360B2 (en) 2000-04-27 2003-06-24 Medtronic Inc. System and method for assessing transmurality of ablation lesions
US6706038B2 (en) 2000-04-27 2004-03-16 Medtronic, Inc. System and method for assessing transmurality of ablation lesions
WO2001080756A1 (en) * 2000-04-27 2001-11-01 Medtronic, Inc. System and method for assessing transmurality of ablation lesions
US20030195496A1 (en) * 2000-05-16 2003-10-16 Maguire Mark A. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US6599288B2 (en) 2000-05-16 2003-07-29 Atrionix, Inc. Apparatus and method incorporating an ultrasound transducer onto a delivery member
US9675403B2 (en) 2000-05-18 2017-06-13 Mederi Therapeutics, Inc. Graphical user interface for monitoring and controlling use of medical devices
US20110190759A1 (en) * 2000-05-18 2011-08-04 Mederi Therapeutics Inc. Graphical user interface for monitoring and controlling use of medical devices
US8845632B2 (en) 2000-05-18 2014-09-30 Mederi Therapeutics, Inc. Graphical user interface for monitoring and controlling use of medical devices
US6752805B2 (en) 2000-06-13 2004-06-22 Atrionix, Inc. Surgical ablation probe for forming a circumferential lesion
US20050149013A1 (en) * 2000-08-09 2005-07-07 Lee Bruce B. Gynecological ablation procedure and system
US7678106B2 (en) 2000-08-09 2010-03-16 Halt Medical, Inc. Gynecological ablation procedure and system
US20080045939A1 (en) * 2000-08-09 2008-02-21 Halt Medical, Inc. Gynecological ablation system with insufflation assisted imaging
US20080045940A1 (en) * 2000-08-09 2008-02-21 Halt Medical, Inc. Gynecological ablation system with laparoscopic and ultrasound imaging
US8177781B2 (en) 2000-10-02 2012-05-15 Novasys Medical, Inc. Apparatus and methods for treating female urinary incontinence
US8465482B2 (en) 2000-10-02 2013-06-18 Verathon, Inc. Apparatus and methods for treating female urinary incontinence
US8968284B2 (en) 2000-10-02 2015-03-03 Verathon Inc. Apparatus and methods for treating female urinary incontinence
US6752804B2 (en) 2000-12-28 2004-06-22 Cardiac Pacemakers, Inc. Ablation system and method having multiple-sensor electrodes to assist in assessment of electrode and sensor position and adjustment of energy levels
KR100776009B1 (en) 2001-01-19 2007-11-16 셀론 아게 메디컬 인스트루먼츠 Device for the electrothermal treatment of the human or animal body
US20040078038A1 (en) * 2001-01-19 2004-04-22 Kai Desinger Device for the electrothermal treatment of the human or animal body
WO2002056782A3 (en) * 2001-01-19 2002-12-12 Celon Ag Medical Instruments Device for the electrothermal treatment of the human or animal body
US20050154433A1 (en) * 2002-03-19 2005-07-14 Solarant Medical, Inc. Heating method for tissue contraction
US7792589B2 (en) * 2002-03-19 2010-09-07 Ams Research Corporation Heating method for tissue contraction
US7008417B2 (en) * 2002-04-22 2006-03-07 Medtronics, Inc. Detecting coagulum formation
US7749217B2 (en) 2002-05-06 2010-07-06 Covidien Ag Method and system for optically detecting blood and controlling a generator during electrosurgery
US20040002740A1 (en) * 2002-05-08 2004-01-01 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US20060083717A1 (en) * 2002-05-08 2006-04-20 Lee Randall J System and method for forming a non-ablative cardiac conduction block
US20070203488A1 (en) * 2002-06-27 2007-08-30 Gyrus Medical Limited Electrosurgical system
US7901401B2 (en) * 2002-06-27 2011-03-08 Gyrus Medical Limited Electrosurgical system
US20040055572A1 (en) * 2002-09-24 2004-03-25 Caterpillar Inc. Hydraulic pump circuit
US20040082947A1 (en) * 2002-10-25 2004-04-29 The Regents Of The University Of Michigan Ablation catheters
US20080161803A1 (en) * 2002-10-25 2008-07-03 The Regents Of The University Of Michigan Ablation Catheters And Methods For Their Use
US7993333B2 (en) 2002-10-25 2011-08-09 The Regents Of The University Of Michigan Ablation catheters
US7857808B2 (en) 2002-10-25 2010-12-28 The Regents Of The University Of Michigan Ablation catheters
US7317950B2 (en) 2002-11-16 2008-01-08 The Regents Of The University Of California Cardiac stimulation system with delivery of conductive agent
US20040098075A1 (en) * 2002-11-16 2004-05-20 The Regents Of The University Of California Cardiac stimulation system and method
US20050271631A1 (en) * 2002-11-29 2005-12-08 Lee Randall J Material compositions and related systems and methods for treating cardiac conditions
US20040106896A1 (en) * 2002-11-29 2004-06-03 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US8523855B2 (en) 2002-12-10 2013-09-03 Covidien Ag Circuit for controlling arc energy from an electrosurgical generator
US7824400B2 (en) 2002-12-10 2010-11-02 Covidien Ag Circuit for controlling arc energy from an electrosurgical generator
US6932804B2 (en) 2003-01-21 2005-08-23 The Regents Of The University Of California System and method for forming a non-ablative cardiac conduction block
US8012150B2 (en) 2003-05-01 2011-09-06 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US8080008B2 (en) 2003-05-01 2011-12-20 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US7722601B2 (en) 2003-05-01 2010-05-25 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US8267929B2 (en) 2003-05-01 2012-09-18 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US8298223B2 (en) 2003-05-01 2012-10-30 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US8303580B2 (en) 2003-05-01 2012-11-06 Covidien Ag Method and system for programming and controlling an electrosurgical generator system
US8647340B2 (en) 2003-10-23 2014-02-11 Covidien Ag Thermocouple measurement system
US8808161B2 (en) 2003-10-23 2014-08-19 Covidien Ag Redundant temperature monitoring in electrosurgical systems for safety mitigation
US8104956B2 (en) 2003-10-23 2012-01-31 Covidien Ag Thermocouple measurement circuit
US9768373B2 (en) 2003-10-30 2017-09-19 Covidien Ag Switched resonant ultrasonic power amplifier system
US8485993B2 (en) 2003-10-30 2013-07-16 Covidien Ag Switched resonant ultrasonic power amplifier system
US8096961B2 (en) 2003-10-30 2012-01-17 Covidien Ag Switched resonant ultrasonic power amplifier system
US8113057B2 (en) 2003-10-30 2012-02-14 Covidien Ag Switched resonant ultrasonic power amplifier system
US8966981B2 (en) 2003-10-30 2015-03-03 Covidien Ag Switched resonant ultrasonic power amplifier system
US7766693B2 (en) 2003-11-20 2010-08-03 Covidien Ag Connector systems for electrosurgical generator
US8192426B2 (en) 2004-01-09 2012-06-05 Tyco Healthcare Group Lp Devices and methods for treatment of luminal tissue
US9393069B2 (en) 2004-01-09 2016-07-19 Covidien Lp Devices and methods for treatment of luminal tissue
US20070149964A1 (en) * 2004-01-27 2007-06-28 Takashi Kawabata Ablation catheter
US7722605B2 (en) * 2004-01-27 2010-05-25 Japan Lifeline Co., Ltd. Ablation catheter
US7766905B2 (en) 2004-02-12 2010-08-03 Covidien Ag Method and system for continuity testing of medical electrodes
US7780662B2 (en) 2004-03-02 2010-08-24 Covidien Ag Vessel sealing system using capacitive RF dielectric heating
US20050267458A1 (en) * 2004-05-27 2005-12-01 Saurav Paul Side-port sheath for catheter placement and translation
US7276064B2 (en) * 2004-05-27 2007-10-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Side-port sheath for catheter placement and translation
US7819871B2 (en) 2004-05-27 2010-10-26 St. Jude Medical, Atrial Fibrillation Division, Inc. Side-port sheath for catheter placement and translation
US20050288662A1 (en) * 2004-06-23 2005-12-29 Uchida Andy H Electrosurgical generator
US7226447B2 (en) 2004-06-23 2007-06-05 Smith & Nephew, Inc. Electrosurgical generator
US20090234351A1 (en) * 2004-08-20 2009-09-17 Kai Desinger Device for the Electro-Surgical Sclerosing of body tissues
DE102004041681A1 (en) * 2004-08-20 2006-02-23 Celon Ag Medical Instruments An apparatus for electrosurgical sclerosing of body tissue
US8221406B2 (en) 2004-08-20 2012-07-17 Celon Ag Medical Instruments Device for the electro-surgical sclerosing of body tissues
US8025660B2 (en) 2004-10-13 2011-09-27 Covidien Ag Universal foot switch contact port
US9642675B2 (en) 2004-10-14 2017-05-09 Medtronic Ablation Frontiers Llc Ablation catheter
US8486063B2 (en) 2004-10-14 2013-07-16 Medtronic Ablation Frontiers Llc Ablation catheter
US8617152B2 (en) 2004-11-15 2013-12-31 Medtronic Ablation Frontiers Llc Ablation system with feedback
US8273084B2 (en) 2004-11-24 2012-09-25 Medtronic Ablation Frontiers Llc Atrial ablation catheter and method of use
US20080275443A1 (en) * 2004-11-24 2008-11-06 Hakan Oral Atrial ablation catheter adapted for treatment of septal wall arrhythmogenic foci and method of use
US9005194B2 (en) 2004-11-24 2015-04-14 Medtronic Ablation Frontiers Llc Atrial ablation catheter adapted for treatment of septal wall arrhythmogenic foci and method of use
US9474564B2 (en) 2005-03-31 2016-10-25 Covidien Ag Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator
US8932208B2 (en) 2005-05-26 2015-01-13 Maquet Cardiovascular Llc Apparatus and methods for performing minimally-invasive surgical procedures
US8979841B2 (en) 2005-06-20 2015-03-17 Medtronic Ablation Frontiers Llc Ablation catheter
US8337492B2 (en) 2005-06-20 2012-12-25 Medtronic Ablation Frontiers Llc Ablation catheter
US9468495B2 (en) 2005-06-20 2016-10-18 Medtronic Ablation Frontiers Llc Ablation catheter
US8771267B2 (en) 2005-06-20 2014-07-08 Medtronic Ablation Frontiers Llc Ablation catheter
US7850685B2 (en) 2005-06-20 2010-12-14 Medtronic Ablation Frontiers Llc Ablation catheter
US7655003B2 (en) 2005-06-22 2010-02-02 Smith & Nephew, Inc. Electrosurgical power control
US8603082B2 (en) 2005-06-22 2013-12-10 Smith & Nephew, Inc. Electrosurgical power control
US8052675B2 (en) 2005-06-22 2011-11-08 Smith & Nephew, Inc. Electrosurgical power control
US20060293649A1 (en) * 2005-06-22 2006-12-28 Lorang Douglas M Electrosurgical power control
US8348934B2 (en) 2005-06-22 2013-01-08 Smith & Nephew, Inc. Electrosurgical power control
US20070016183A1 (en) * 2005-07-01 2007-01-18 Bruce Lee Radio frequency ablation device for the destruction of tissue masses
US8080009B2 (en) 2005-07-01 2011-12-20 Halt Medical Inc. Radio frequency ablation device for the destruction of tissue masses
US20070006215A1 (en) * 2005-07-01 2007-01-04 Gordon Epstein Anchored RF ablation device for the destruction of tissue masses
US8512333B2 (en) 2005-07-01 2013-08-20 Halt Medical Inc. Anchored RF ablation device for the destruction of tissue masses
US8834461B2 (en) 2005-07-11 2014-09-16 Medtronic Ablation Frontiers Llc Low power tissue ablation system
US9566113B2 (en) 2005-07-11 2017-02-14 Medtronic Ablation Frontiers Llc Low power tissue ablation system
US8657814B2 (en) 2005-08-22 2014-02-25 Medtronic Ablation Frontiers Llc User interface for tissue ablation system
US20070083193A1 (en) * 2005-08-22 2007-04-12 Werneth Randell L User interface for tissue ablation system
US20070055225A1 (en) * 2005-09-07 2007-03-08 Dodd Gerald D Iii Method and apparatus for electromagnetic ablation of biological tissue
US8734438B2 (en) 2005-10-21 2014-05-27 Covidien Ag Circuit and method for reducing stored energy in an electrosurgical generator
US9522032B2 (en) 2005-10-21 2016-12-20 Covidien Ag Circuit and method for reducing stored energy in an electrosurgical generator
US9918793B2 (en) 2005-11-23 2018-03-20 Covidien Lp Auto-aligning ablating device and method of use
US9179970B2 (en) 2005-11-23 2015-11-10 Covidien Lp Precision ablating method
US9918794B2 (en) 2005-11-23 2018-03-20 Covidien Lp Auto-aligning ablating device and method of use
US8702695B2 (en) 2005-11-23 2014-04-22 Covidien Lp Auto-aligning ablating device and method of use
US7997278B2 (en) 2005-11-23 2011-08-16 Barrx Medical, Inc. Precision ablating method
US8702694B2 (en) 2005-11-23 2014-04-22 Covidien Lp Auto-aligning ablating device and method of use
US7959627B2 (en) 2005-11-23 2011-06-14 Barrx Medical, Inc. Precision ablating device
US8998890B2 (en) 2005-12-06 2015-04-07 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9271782B2 (en) 2005-12-06 2016-03-01 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling of tissue ablation
US20110118727A1 (en) * 2005-12-06 2011-05-19 Fish Jeffrey M System and method for assessing the formation of a lesion in tissue
US20110144524A1 (en) * 2005-12-06 2011-06-16 Fish Jeffrey M Graphical user interface for real-time rf lesion depth display
US9283026B2 (en) 2005-12-06 2016-03-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9492226B2 (en) 2005-12-06 2016-11-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Graphical user interface for real-time RF lesion depth display
US9283025B2 (en) 2005-12-06 2016-03-15 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9173586B2 (en) 2005-12-06 2015-11-03 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing coupling between an electrode and tissue
US8603084B2 (en) 2005-12-06 2013-12-10 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing the formation of a lesion in tissue
US9254163B2 (en) 2005-12-06 2016-02-09 St. Jude Medical, Atrial Fibrillation Division, Inc. Assessment of electrode coupling for tissue ablation
US9339325B2 (en) 2005-12-06 2016-05-17 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing lesions in tissue
US8241278B2 (en) 2005-12-12 2012-08-14 Covidien Ag Laparoscopic apparatus for performing electrosurgical procedures
US7947039B2 (en) 2005-12-12 2011-05-24 Covidien Ag Laparoscopic apparatus for performing electrosurgical procedures
US7927328B2 (en) 2006-01-24 2011-04-19 Covidien Ag System and method for closed loop monitoring of monopolar electrosurgical apparatus
US8187262B2 (en) 2006-01-24 2012-05-29 Covidien Ag Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling
US8202271B2 (en) 2006-01-24 2012-06-19 Covidien Ag Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling
US9186200B2 (en) 2006-01-24 2015-11-17 Covidien Ag System and method for tissue sealing
US8216223B2 (en) 2006-01-24 2012-07-10 Covidien Ag System and method for tissue sealing
US7972328B2 (en) 2006-01-24 2011-07-05 Covidien Ag System and method for tissue sealing
US8663214B2 (en) 2006-01-24 2014-03-04 Covidien Ag Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm
US8267928B2 (en) 2006-01-24 2012-09-18 Covidien Ag System and method for closed loop monitoring of monopolar electrosurgical apparatus
US8685016B2 (en) 2006-01-24 2014-04-01 Covidien Ag System and method for tissue sealing
US9642665B2 (en) 2006-01-24 2017-05-09 Covidien Ag Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm
US8475447B2 (en) 2006-01-24 2013-07-02 Covidien Ag System and method for closed loop monitoring of monopolar electrosurgical apparatus
US8147485B2 (en) 2006-01-24 2012-04-03 Covidien Ag System and method for tissue sealing
US7972332B2 (en) 2006-03-03 2011-07-05 Covidien Ag System and method for controlling electrosurgical snares
US7651493B2 (en) 2006-03-03 2010-01-26 Covidien Ag System and method for controlling electrosurgical snares
US7648499B2 (en) 2006-03-21 2010-01-19 Covidien Ag System and method for generating radio frequency energy
US8556890B2 (en) 2006-04-24 2013-10-15 Covidien Ag Arc based adaptive control system for an electrosurgical unit
US7651492B2 (en) 2006-04-24 2010-01-26 Covidien Ag Arc based adaptive control system for an electrosurgical unit
US9119624B2 (en) 2006-04-24 2015-09-01 Covidien Ag ARC based adaptive control system for an electrosurgical unit
US8753334B2 (en) 2006-05-10 2014-06-17 Covidien Ag System and method for reducing leakage current in an electrosurgical generator
US9345900B2 (en) 2006-06-28 2016-05-24 Medtronic Ardian Luxembourg S.A.R.L. Methods and systems for thermally-induced renal neuromodulation
US9314644B2 (en) 2006-06-28 2016-04-19 Medtronic Ardian Luxembourg S.A.R.L. Methods and systems for thermally-induced renal neuromodulation
US20080255642A1 (en) * 2006-06-28 2008-10-16 Ardian, Inc. Methods and systems for thermally-induced renal neuromodulation
US8034049B2 (en) 2006-08-08 2011-10-11 Covidien Ag System and method for measuring initial tissue impedance
US7731717B2 (en) 2006-08-08 2010-06-08 Covidien Ag System and method for controlling RF output during tissue sealing
US8486060B2 (en) 2006-09-18 2013-07-16 Cytyc Corporation Power ramping during RF ablation
US7794457B2 (en) 2006-09-28 2010-09-14 Covidien Ag Transformer for RF voltage sensing
US8231616B2 (en) 2006-09-28 2012-07-31 Covidien Ag Transformer for RF voltage sensing
US8403925B2 (en) 2006-12-06 2013-03-26 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for assessing lesions in tissue
US20090138011A1 (en) * 2007-03-13 2009-05-28 Gordon Epstein Intermittent ablation rf driving for moderating return electrode temperature
US8641711B2 (en) 2007-05-04 2014-02-04 Covidien Lp Method and apparatus for gastrointestinal tract ablation for treatment of obesity
US8777941B2 (en) 2007-05-10 2014-07-15 Covidien Lp Adjustable impedance electrosurgical electrodes
US8771269B2 (en) 2007-05-11 2014-07-08 Medtronic Ablation Frontiers Llc RF energy delivery system and method
US8641704B2 (en) 2007-05-11 2014-02-04 Medtronic Ablation Frontiers Llc Ablation therapy system and method for treating continuous atrial fibrillation
US8784338B2 (en) 2007-06-22 2014-07-22 Covidien Lp Electrical means to normalize ablational energy transmission to a luminal tissue surface of varying size
US9198713B2 (en) 2007-06-22 2015-12-01 Covidien Lp Electrical means to normalize ablational energy transmission to a luminal tissue surface of varying size
US9839466B2 (en) 2007-07-06 2017-12-12 Covidien Lp Method and apparatus for gastrointestinal tract ablation to achieve loss of persistent and/or recurrent excess body weight following a weight loss operation
US8439908B2 (en) 2007-07-06 2013-05-14 Covidien Lp Ablation in the gastrointestinal tract to achieve hemostasis and eradicate lesions with a propensity for bleeding
US9364283B2 (en) 2007-07-06 2016-06-14 Covidien Lp Method and apparatus for gastrointestinal tract ablation to achieve loss of persistent and/or recurrent excess body weight following a weight loss operation
US8251992B2 (en) 2007-07-06 2012-08-28 Tyco Healthcare Group Lp Method and apparatus for gastrointestinal tract ablation to achieve loss of persistent and/or recurrent excess body weight following a weight-loss operation
US7834484B2 (en) 2007-07-16 2010-11-16 Tyco Healthcare Group Lp Connection cable and method for activating a voltage-controlled generator
US8273012B2 (en) 2007-07-30 2012-09-25 Tyco Healthcare Group, Lp Cleaning device and methods
US9314289B2 (en) 2007-07-30 2016-04-19 Covidien Lp Cleaning device and methods
US8646460B2 (en) 2007-07-30 2014-02-11 Covidien Lp Cleaning device and methods
US8216220B2 (en) 2007-09-07 2012-07-10 Tyco Healthcare Group Lp System and method for transmission of combined data stream
US8353905B2 (en) 2007-09-07 2013-01-15 Covidien Lp System and method for transmission of combined data stream
US9271790B2 (en) 2007-09-21 2016-03-01 Coviden Lp Real-time arc control in electrosurgical generators
US8512332B2 (en) 2007-09-21 2013-08-20 Covidien Lp Real-time arc control in electrosurgical generators
US8251991B2 (en) 2007-11-14 2012-08-28 Halt Medical Inc. Anchored RF ablation device for the destruction of tissue masses
US8241276B2 (en) 2007-11-14 2012-08-14 Halt Medical Inc. RF ablation device with jam-preventing electrical coupling member
US20090187182A1 (en) * 2007-11-14 2009-07-23 Gordon Epstein Rf ablation device with jam-preventing electrical coupling member
US8290578B2 (en) * 2007-12-28 2012-10-16 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for complex impedance compensation
US20090171235A1 (en) * 2007-12-28 2009-07-02 Clint Schneider Method and apparatus for complex impedance compensation and for determining tissue morphology based on phase angle
US8551088B2 (en) 2008-03-31 2013-10-08 Applied Medical Resources Corporation Electrosurgical system
US9566108B2 (en) 2008-03-31 2017-02-14 Applied Medical Resources Corporation Electrosurgical system
US8579894B2 (en) 2008-03-31 2013-11-12 Applied Medical Resources Corporation Electrosurgical system
US20090248007A1 (en) * 2008-03-31 2009-10-01 Applied Medical Resources Corporation Electrosurgical system
US8568411B2 (en) 2008-03-31 2013-10-29 Applied Medical Resources Corporation Electrosurgical system
US8562598B2 (en) 2008-03-31 2013-10-22 Applied Medical Resources Corporation Electrosurgical system
US8915910B2 (en) 2008-03-31 2014-12-23 Applied Medical Resources Corporation Electrosurgical system
EP2498509A2 (en) 2008-04-07 2012-09-12 Koss Corporation Wireless earphone that transitions between wireless networks
US8226639B2 (en) 2008-06-10 2012-07-24 Tyco Healthcare Group Lp System and method for output control of electrosurgical generator
US8920412B2 (en) 2008-06-30 2014-12-30 Erbe Elektromedizin Gmbh Electrosurgical generator for the treatment of a biological tissue, method for regulating an output voltage of an electrosurgical generator, and corresponding use of the electrosurgical generator
WO2010000362A1 (en) * 2008-06-30 2010-01-07 Erbe Elektromedizin Gmbh Electrosurgical generator for the treatment of a biological tissue, method for regulating an output voltage of an electrosurgical generator, and corresponding use of the electrosurgical generator
US20110112526A1 (en) * 2008-06-30 2011-05-12 Martin Fritz Electrosurgical generator for the treatment of a biological tissue, method for regulating an output voltage of an electrosurgical generator, and corresponding use of the electrosurgical generator
US8486061B2 (en) 2009-01-12 2013-07-16 Covidien Lp Imaginary impedance process monitoring and intelligent shut-off
US9265556B2 (en) 2009-04-17 2016-02-23 Domain Surgical, Inc. Thermally adjustable surgical tool, balloon catheters and sculpting of biologic materials
US9265553B2 (en) 2009-04-17 2016-02-23 Domain Surgical, Inc. Inductively heated multi-mode surgical tool
US9265554B2 (en) 2009-04-17 2016-02-23 Domain Surgical, Inc. Thermally adjustable surgical system and method
US9131977B2 (en) 2009-04-17 2015-09-15 Domain Surgical, Inc. Layered ferromagnetic coated conductor thermal surgical tool
US8506561B2 (en) 2009-04-17 2013-08-13 Domain Surgical, Inc. Catheter with inductively heated regions
US20100268208A1 (en) * 2009-04-17 2010-10-21 Kim Manwaring Surgical scalpel with inductively heated regions
US8491578B2 (en) 2009-04-17 2013-07-23 Domain Surgical, Inc. Inductively heated multi-mode bipolar surgical tool
US9265555B2 (en) 2009-04-17 2016-02-23 Domain Surgical, Inc. Multi-mode surgical tool
US8617151B2 (en) 2009-04-17 2013-12-31 Domain Surgical, Inc. System and method of controlling power delivery to a surgical instrument
US9549774B2 (en) 2009-04-17 2017-01-24 Domain Surgical, Inc. System and method of controlling power delivery to a surgical instrument
US8523850B2 (en) 2009-04-17 2013-09-03 Domain Surgical, Inc. Method for heating a surgical implement
US8430870B2 (en) 2009-04-17 2013-04-30 Domain Surgical, Inc. Inductively heated snare
US9320560B2 (en) 2009-04-17 2016-04-26 Domain Surgical, Inc. Method for treating tissue with a ferromagnetic thermal surgical tool
US20100268210A1 (en) * 2009-04-17 2010-10-21 Kim Manwaring Inductively heated surgical implement driver
US8425503B2 (en) 2009-04-17 2013-04-23 Domain Surgical, Inc. Adjustable ferromagnetic coated conductor thermal surgical tool
US9107666B2 (en) 2009-04-17 2015-08-18 Domain Surgical, Inc. Thermal resecting loop
US8419724B2 (en) 2009-04-17 2013-04-16 Domain Surgical, Inc. Adjustable ferromagnetic coated conductor thermal surgical tool
US8414569B2 (en) 2009-04-17 2013-04-09 Domain Surgical, Inc. Method of treatment with multi-mode surgical tool
US9078655B2 (en) 2009-04-17 2015-07-14 Domain Surgical, Inc. Heated balloon catheter
US9730749B2 (en) 2009-04-17 2017-08-15 Domain Surgical, Inc. Surgical scalpel with inductively heated regions
US9220557B2 (en) 2009-04-17 2015-12-29 Domain Surgical, Inc. Thermal surgical tool
US8523852B2 (en) * 2009-04-17 2013-09-03 Domain Surgical, Inc. Thermally adjustable surgical tool system
US9204927B2 (en) 2009-05-13 2015-12-08 St. Jude Medical, Atrial Fibrillation Division, Inc. System and method for presenting information representative of lesion formation in tissue during an ablation procedure
US9474565B2 (en) 2009-09-22 2016-10-25 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9750563B2 (en) 2009-09-22 2017-09-05 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9495059B2 (en) 2009-09-22 2016-11-15 Mederi Therapeutics, Inc. Systems and methods for controlling use and operation of a family of different treatment devices
US9775664B2 (en) 2009-09-22 2017-10-03 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9513761B2 (en) 2009-09-22 2016-12-06 Mederi Therapeutics, Inc. Systems and methods for controlling use of treatment devices
US9448681B2 (en) 2009-09-22 2016-09-20 Mederi Therapeutics, Inc. Systems and methods for controlling use and operation of a family of different treatment devices
US9675404B2 (en) 2009-09-22 2017-06-13 Mederi Therapeutics, Inc. Systems and methods for treating tissue with radiofrequency energy
US9310956B2 (en) 2009-09-22 2016-04-12 Mederi Therapeutics, Inc. Systems and methods for controlling use and operation of a family of different treatment devices
US9292152B2 (en) 2009-09-22 2016-03-22 Mederi Therapeutics, Inc. Systems and methods for controlling use and operation of a family of different treatment devices
US20110071518A1 (en) * 2009-09-24 2011-03-24 Tyco Healthcare Group Lp System and Method for Multi-Pole Phase-Shifted Radio Frequency Application
US8685015B2 (en) 2009-09-24 2014-04-01 Covidien Lp System and method for multi-pole phase-shifted radio frequency application
US20110071516A1 (en) * 2009-09-24 2011-03-24 Tyco Healthcare Group Lp System and Method for Controlling Electrosurgical Output
EP2301462A1 (en) * 2009-09-24 2011-03-30 Tyco Healthcare Group, LP Electrosurgical generator for controlling output in response to voltage and current phases
US9265574B2 (en) * 2010-03-10 2016-02-23 Biosense Webster (Israel) Ltd. Monitoring tissue temperature while using an irrigated catheter
US20110224573A1 (en) * 2010-03-10 2011-09-15 Bar-Tal Meir Monitoring tissue temperature while using an irrigated catheter
US9962222B2 (en) 2010-10-01 2018-05-08 Applied Medical Resources Corporation Electrosurgical instruments and connections thereto
US9320563B2 (en) 2010-10-01 2016-04-26 Applied Medical Resources Corporation Electrosurgical instruments and connections thereto
US9066720B2 (en) 2010-10-25 2015-06-30 Medtronic Ardian Luxembourg S.A.R.L. Devices, systems and methods for evaluation and feedback of neuromodulation treatment
US9750560B2 (en) 2010-10-25 2017-09-05 Medtronic Ardian Luxembourg S.A.R.L. Devices, systems and methods for evaluation and feedback of neuromodulation treatment
US9345530B2 (en) 2010-10-25 2016-05-24 Medtronic Ardian Luxembourg S.A.R.L. Devices, systems and methods for evaluation and feedback of neuromodulation treatment
US9980772B2 (en) 2011-02-28 2018-05-29 Biosense Webster (Israel) Ltd. Monitoring tissue temperature while using an irrigated catheter
US20120239024A1 (en) * 2011-03-17 2012-09-20 Vivant Medical, Inc. Energy-Based Ablation Completion Algorithm
US8932279B2 (en) 2011-04-08 2015-01-13 Domain Surgical, Inc. System and method for cooling of a heated surgical instrument and/or surgical site and treating tissue
US9149321B2 (en) 2011-04-08 2015-10-06 Domain Surgical, Inc. System and method for cooling of a heated surgical instrument and/or surgical site and treating tissue
US8915909B2 (en) 2011-04-08 2014-12-23 Domain Surgical, Inc. Impedance matching circuit
US9526558B2 (en) 2011-09-13 2016-12-27 Domain Surgical, Inc. Sealing and/or cutting instrument
US8403927B1 (en) 2012-04-05 2013-03-26 William Bruce Shingleton Vasectomy devices and methods
WO2013162884A1 (en) * 2012-04-26 2013-10-31 Medtronic Ablation Frontiers Llc System for detecting tissue contact during ablation
US9750570B2 (en) 2012-05-01 2017-09-05 Medtronic Ablation Frontiers Llc Systems and methods for detecting tissue contact during ablation
CN104582615A (en) * 2012-06-27 2015-04-29 麦迪尼治疗公司 Systems and methods for treating tissue with radio frequency energy
CN104582615B (en) * 2012-06-27 2017-02-22 麦迪尼治疗公司 Using radio frequency energy to tissue treatment systems and methods
US9872719B2 (en) 2013-07-24 2018-01-23 Covidien Lp Systems and methods for generating electrosurgical energy using a multistage power converter
US9636165B2 (en) 2013-07-29 2017-05-02 Covidien Lp Systems and methods for measuring tissue impedance through an electrosurgical cable
US9655670B2 (en) 2013-07-29 2017-05-23 Covidien Lp Systems and methods for measuring tissue impedance through an electrosurgical cable
US20150045976A1 (en) * 2013-08-09 2015-02-12 The Boeing Company Advanced energy monitoring and control in a complex system
US9577432B2 (en) * 2013-08-09 2017-02-21 The Boeing Company Advanced energy monitoring and control in a complex system
USD748259S1 (en) 2014-12-29 2016-01-26 Applied Medical Resources Corporation Electrosurgical instrument
US20160338768A1 (en) * 2015-05-18 2016-11-24 Biosense Webster (Israel) Ltd. Catheter with coaxial thermocouple

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CA2106409A1 (en) 1993-05-09 application
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EP0566731A4 (en) 1995-02-22 application
JPH07500756A (en) 1995-01-26 application

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